Inhaler

ABSTRACT

An inhaler, preferably for insertion into a nostril, in particular a horse&#39;s nostril, with a pressure generator, which has a tensioning device for the drive, and with a tensioning mechanism for tensioning the tensioning device, whereby the tensioning mechanism has a lever gear for tensioning the tensioning device.

BACKGROUND OF THE INVENTION

Field of the Invention

This invention relates to an inhaler, preferably for insertion into anostril, in particular a horse's nostril, with a pressure generator,which has a tensioning device for driving and a tensioning mechanism fortensioning the tensioning device and to a use and method of a nebulizeror inhaler.

Description of Related Art

This invention relates in particular to a so-called Soft Mist Inhaler(SMI), i.e., an inhaler that produces an atomized spray (aerosol) thatpropagates only comparatively slowly. In terms of this invention, suchinhalers are in particular inhalers in which an aerosol is dispensed ata speed of less than 2 m/s, preferably approximately 1.6 m/s or less,and quite especially preferably less than 1 m/s (in each case measuredat a distance of 10 cm from a discharge nozzle) and/or in which thedispensing or spraying of a dose—of preferably 10 to 50 μl of apharmaceutical agent preparation—lasts longer than 0.7 s, in particularapproximately 1 s or longer.

International Patent Application Publication WO 2005/079997 A1 andcorresponding U.S. Pat. No. 7,571,722 disclose an inhaler thatrepresents an SMI in terms of this invention. As a reservoir for apharmaceutical agent preparation that is to be sprayed, the knowninhaler has an insertable, rigid container with an inner bag with thepharmaceutical agent preparation and a pressure generator with amainspring for delivery and spraying of the pharmaceutical agentpreparation. The spraying is done without propellant, namely under theaction of the force of the mainspring.

It is problematic in the case of inhalers and even SMIs in general thata consistent amount of active ingredient is to be administered. Onlywith manual operation can it be difficult to meter exactly the amount ofactive ingredient administered, i.e., in particular the amount of thesprayed pharmaceutical agent preparation.

International Patent Application Publication WO 2004/091704 A1 andcorresponding U.S. Pat. No. 7,360,537 disclose an additional device forintermediate storage of a sprayed pharmaceutical agent preparation in achamber, also called a spacer. The additional device is inserted into aso-called Metered Dose Inhaler (MDI). An MDI has a tensioned containerthat contains the pharmaceutical agent preparation to be sprayed as wellas propellant. Upon actuation, the propellant causes the pharmaceuticalagent preparation to be dispensed at comparatively high pressure andcorrespondingly high speed and with a high mass stream. Therefore, thedispensing occurs for only a very short time, in particular for lessthan 0.4 s, and in most cases for approximately 0.15-0.39 s. The shortdispensing time is disadvantageous for an inhalation, since the intakefor inhalation usually lasts significantly longer. The comparativelyhigh speed of more than 2 m/s, often even up to or over 8 m/s, withwhich the aerosol is usually administered by an MDI, is alsodisadvantageous for uptake into the lungs, since the particles(droplets) of the aerosol are deposited for the most part on the wall ofthe user's throat because of the high speed in the case of directinhalation.

The known additional device is provided for an MDI and serves to slowdown the aerosol, in particular by lengthening the flow path. For thisreason, such additional devices are also called spacers. In addition,the additional device serves to ensure intermediate storage for theaerosol that is realized.

International Patent Application Publication WO 01/78818 A2 andcorresponding U.S. Pat. No. 6,644,305 disclose an inhaler for the nose.The inhaler has a pump cylinder that can be actuated manually and anadapter, arranged thereon, with a chamber for intermediate storage of anaerosol that is produced. The pump cylinder is not an SMI in terms ofthis invention. Rather, a short and strong actuation of the pumpcylinder is necessary in order to achieve an acceptable spraying, sothat the characteristics correspond to those of an MDI, if, by means ofthe pump cylinder, an aerosol can be produced at all with the very smalldroplets desired for inhalation in the lungs.

International Patent Application Publication WO 94/17753 A1 andcorresponding U.S. Pat. No. 5,666,948 disclose an inhalation device forlarge animals, such as horses. The inhalation device comprises an MDI,which releases an aerosol in an additional device with a tubularsection. The aerosol is sprayed in the longitudinal direction of thetubular section. A soft adapter can be connected to the tubular section,which adapter is designed for insertion into a horse's nostril.According to a variant embodiment, the inhalation device has a handlewith a corresponding, manually actuatable, pivotable actuating element.Upon actuation of the actuating element, the MDI is shifted linearly,ensuring that a metering valve of the MDIs is opened and aerosol isreleased into the tubular section. In the case of MDIs, it isdisadvantageous that the spraying is carried out by propellant. Further,the operation is problematic. The direction in which the actuatingelement can be actuated manually runs parallel to the longitudinalextension of the tubular section or additional device, so that anoperator intuitively positions himself on the side opposite theadministration side of the additional device; this is verydisadvantageous, however, for the application in the case of a horsewhen the operator would like to hold the horse at the same time.

International Patent Application Publication WO 2010/149280 and U.S.Patent Application Publication 2012/0103326 A1 relate to a Soft MistInhaler with a tension spring and a tensioning mechanism that canpressurize the tension spring, so that hereinafter, the latter can drivea pump for discharging a pharmaceutical agent mixture, by which anaerosol is formed. In a variant, the tensioning mechanism has anoperating lever, with which a one-handed operation is made possible. Theoperating lever has a hinged gear rack, by means of which a rotationalmovement can be realized from a pivoting movement of the operating leverin order to pressurize the tension spring. Because of numerous deviationprocesses, the tensioning mechanism has comparatively large frictionlosses, which is unfavorable for fatigue-free, easy operation.Furthermore, it can happen that the operating lever is not pivoted allthe way to the stop. In this case, the aerosol can be dispensedimmediately, i.e., without triggering, and in a dosage that is too smallor that deviates in some other way.

SUMMARY OF THE INVENTION

The object of this invention is to provide an inhaler, especiallypreferably an SMI, which enables a comfortable activation and/or whereina reliable metering can be facilitated.

The above object is achieved by an inhaler, a nebulizer and method asdescribed herein.

According to a first main aspect of this invention, the tensioningmechanism has a lever gear for tensioning the tensioning device. Unlikeknown tensioning mechanisms, a lever gear has the advantage that in thisway, friction-free tensioning and therefore an inhaler, in particular anSMI, can be achieved that can be operated comfortably, without fatigue,and/or with little effort.

According to another main aspect of this invention that can also beachieved independently, the tensioning mechanism is configured torequire less force for further tensioning of the tensioning device in atensioning process with increasing tensioning of the tensioning device.It is thus provided that the tensioning process requires less forcetoward the end; the tensioning toward the end of the tensioning processis thus easier or simpler. In this way, it can be achieved in anadvantageous manner that the tensioning process is reliably conductedall the way up to the end.

In particular, it is provided that the tensioning mechanism generates adecreasing counterforce at least in one area before reaching atensioning position, so that with increasing tensioning, the force to beapplied decreases. The effect of this is that the tensioning process, onthe one hand, can be performed very easily up until the end; on theother hand, a user reacts late to changes in the force to be applied orthe counterforce. As a result of the necessary force decreasing, thetensioning process is accelerated when using the same force, by whichreliably a final position of the tensioning mechanism is achieved. Bycomplete implementation of the tensioning process, it can be ensuredthat the intended metering by the inhaler can always be maintained.Therefore, the inhaler according to the proposal can be metered in anespecially reliable and exact manner.

Another aspect of this invention that can also be achieved independentlyrelates to an inhaler, preferably for use in a nostril, in particular ahorse's nostril, with a pressure generator, which comprises a tensioningdevice for the drive, whereby the tensioning device can be tensioned insuch a way that a tensioning part, in particular an actuating lever, ismoved from a first position, in particular a position of rest, of thetensioning part into a second position, in particular the tensionedposition, of the tensioning part, wherein the inhaler is designed toblock the drive of the pressure generator and/or the discharge of apharmaceutical agent preparation, and to release the drive of thepressure generator and/or to effect discharge of a pharmaceutical agentpreparation by moving the tensioning part from the first position in thedirection of the second position again after the tensioning part hasbeen moved from the second position back into the first position.

It has been shown that triggering elements realized separately from thetensioning mechanism are difficult to operate in particular when used inconnection with the application on (large) animals or when using gloves.It has further been shown that during automatic triggering at the end ofa tensioning process, no sufficiently exact timing for the discharge ofthe pharmaceutical agent preparation can be determined. This is relevantin particular in application on (large) animals, since influence on therespiratory activity is not possible in this case and consequently thetriggering must be adapted to the respiratory activity. The solutionaccording to the proposal combines the advantage of a sturdy design witha triggering control that is timely precise, since it is not necessaryto switch hands, and triggering can be done with the movement alreadyknown from the tensioning process.

The above-mentioned aspects and features can be realized independentlyof one another, and also in any combination.

Other advantages, features, properties, and aspects of this inventionwill become apparent from the following description in conjunction withthe accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a side view of an inhaler according to the invention in anostril;

FIG. 2 is a sectional view of the inhaler in the area of the pressuregenerator in an untensioned state;

FIG. 3 is a sectional view of the inhaler in the area of the pressuregenerator in a tensioned state;

FIG. 4 is a sectional view of the inhaler in the area of the lever gearin the rest position;

FIG. 5 is a sectional of the inhaler in the area of the lever gear inthe tensioned position;

FIG. 6 is a simplified, perspective view of the inhaler in the area ofthe indicator for display of doses that are still available or alreadyadministered with a pump device and tensioning device;

FIG. 7 is a simplified, perspective view of the inhaler in the area ofthe indicator for display of doses that are still available or alreadyadministered without the pump device;

FIG. 8 is an exploded perspective view of an inhalation valve accordingto the invention;

FIG. 9 is a simplified, partial sectional view of the inhaler in thearea of the inhalation valve in a closed state;

FIG. 10 is a simplified, partial sectional view of the inhaler in thearea of the inhalation valve in an open state;

FIG. 11 is a sectional view of the chamber with a dispensing device ofthe inhalerin the area of the respiration indicator in the restposition;

FIG. 12 is a sectional view of the chamber with a dispensing device ofthe inhalerin the area of the respiration indicator in the expiratoryposition;

FIG. 13 is a sectional view of the chamber with a dispensing device ofthe inhalerin the area of the respiration indicator in the inhalationposition;

FIG. 14 is a sectional view of the chamber with a dispensing device ofthe inhalerin the area of the respiration indicator in accordance withan alternative embodiment in the rest position;

FIG. 15 is a sectional view of the chamber with a dispensing device ofthe inhalerin the area of the respiration indicator in accordance withan alternative embodiment in the expiratory position;

FIG. 16 is a sectional view of the chamber with a dispensing device ofthe inhalerin the area of the respiration indicator in accordance withan alternative embodiment in the inhalation position;

FIG. 17 is a side view of the inhaler in accordance with a secondembodiment of the invention;

FIG. 18 is a side view of the inhaler in accordance with a secondembodiment of the invention with the outside shell of the container ofthe pressure generator removed;

FIG. 19 is perspective view of the tensioning device of the pressuregenerator in accordance with the second embodiment;

FIG. 20 is a perspective view of a pivot arm of the inhaler inaccordance with the second embodiment;

FIG. 21 is a view corresponding to that of FIG. 18 showing the pressuregenerator in accordance with the second embodiment with an actuatinglever in the rest position;

FIG. 22 is a view corresponding to that of FIG. 18 showing the pressuregenerator in accordance with the second embodiment with an actuatinglever in the tensioned position;

FIG. 23 is a view corresponding to that of FIG. 18 showing the pressuregenerator in accordance with the second embodiment with an actuatinglever in the rest position with a tensioned tensioning device; and

FIG. 24 is a view corresponding to that of FIG. 18 showing the pressuregenerator in accordance with the second embodiment with the actuatinglever at the trigger point.

DETAILED DESCRIPTION OF THE INVENTION

In the figures, the same reference numbers are used for identical orsimilar parts, whereby corresponding or comparable properties andadvantages can be achieved even if a description is not repeated.

FIG. 1 shows a view of an inhaler 1 according to the invention. Theinhaler 1 has a discharge nozzle 2 that is indicated in dotted lines inFIG. 1 and that preferably is designed for forming an aerosol 3 with apharmaceutical agent preparation 4.

When spraying the pharmaceutical agent preparation 4, preferably aliquid, the preferably respirable aerosol 3 is formed, which can bebreathed in or inhaled by a user or patient, not shown, such as ananimal, a human, or preferably a large animal, in particular a horse 5.Usually, the inhalation is done at least once daily, in particularseveral times daily, preferably at predetermined time intervals, inparticular based on the disease.

The inhaler 1 preferably has a dispensing device 7 for fluidicconnection of the chamber 6 to a bodily orifice, preferably a nostril 9,in particular the nostril of a horse 5. The dispensing device 7 ispreferably formed in one piece with the chamber 6 or is connected to thelatter.

The aerosol 3 can be intermediately stored in a chamber 6 and/oradministered by the dispensing device 7.

The chamber 6 is preferably designed for uptake and/or intermediatestorage of the aerosol 3 that is realized by the inhaler 1. The chamber6 is preferably arranged or can be arranged downstream from thedischarge nozzle 2. The chamber 6 can be designed at least partially ina tubular, cylindrical, elongated or conical manner.

In the illustrated embodiment, the introduction of the aerosol 3 intothe chamber 6 is done in the spraying direction of the discharge nozzle2, along a lengthwise extension of the inhaler 1, or in the direction offlow in the area of the discharge nozzle 2, or axially or in thedirection of the longitudinal axis L.

The chamber 6 and the dispensing device 7 can be formed separately or inmultiple pieces, for example by a connection in the area of theconnecting line 8 indicated in dotted lines. In the illustratedembodiment, the chamber 6 is formed in one piece with the dispensingdevice 7, in particular an adapter for a body orifice, in particular anose or nostril 9. In this way, recesses and gaps, to which contaminantscan adhere or into which they can enter, can be avoided.

The chamber 6 is preferably designed in an at least essentially rigidmanner. However, in principle, the chamber 6 can also be designed to beflexible and/or telescoping, in particular to be able to minimize thespace requirement when not in use and/or for transport. In theillustrated embodiment, the chamber 6 is formed from a dimensionallystable, flexible material, and in terms of fluid engineering, thechamber 6 turns seamlessly into the dispensing device 7 in order toensure a continuous path of flow. It is not ruled out, however, that thedispensing device 7 is connected to the chamber 6 in a resting and/orclamping manner and/or with a bayonet closure, with screw threading, orthe like. Here also, however, other design solutions are possible.

The dispensing device 7 preferably has a soft end piece or forms thelatter.

The dispensing device 7 is preferably designed as a nose adapter forinsertion into the nostril 9 of the horse 5 or another animal, inparticular a large animal, as indicated in a diagrammatic, cutaway viewin FIG. 1. In particular, the inhaler 1 or the chamber 6 or thedispensing device 7 is thus designed in such a way that the aerosol 3can be introduced into preferably the left nostril 9 of the horse 5. Thechamber 6 and/or the dispensing device 7 can be transparent or formedfrom transparent plastic. In this way, the forming of aerosol 3 can becontrolled.

Here, the dispensing device 7 preferably comprises an outlet 10, whichengages or can be inserted into the nostril 9 or a nasal passage 11 of ahorse 5 or another bodily orifice, and the chamber 6 or the dispensingdevice 7 can connect in a fluidic manner to the bodily orifice. Thedispensing device 7 is especially preferably designed in such a way thatthe outlet 10 always ends in the correct nasal passage 11 and not in ablind passage. The dispensing device 7 can be at least essentiallydesigned as described in International Patent Application Publication WO94/17753 A1 and corresponding U.S. Pat. No. 5,666,948.

The user or patient, in particular a horse 5, can inhale the aerosol 3,whereby preferably air can be sucked in through the chamber 6.

The chamber 6 preferably comprises a volume of more than 0.05 l, inparticular more than 0.1 l, and especially preferably approximately 0.1to 0.4 l. Preferably, the size of the chamber 6 is matched or adapted tothe inhaler 1 in such a way that the aerosol 3 that is generated whenactuating the inhaler 1 can be taken up at least essentially completelyfrom the chamber 6, in particular without the aerosol 3 or the sprayedpharmaceutical agent preparation 4 being significantly precipitated ordeposited on the inside wall of the chamber.

In FIGS. 2 and 3, a cutaway of the inhaler 1, according to theinvention, is shown in the untensioned and the tensioned states.

The inhaler 1 is designed in particular as a Soft Mist Inhaler in theabove-mentioned sense. The latter is explained in more detail belowbased on the cutaways according to FIGS. 2 and 3.

The inhaler 1 preferably comprises a container 12 with thepharmaceutical agent preparation 4. The container 12 thus forms areservoir for the pharmaceutical agent preparation 4 that is to besprayed. The container 12 preferably contains an adequate amount ofpharmaceutical agent preparation 4 or active ingredient for multipledoses of the pharmaceutical agent preparation 4, i.e., to make possiblemultiple sprayings or applications. As disclosed in International PatentApplication Publication WO 96/06011 A1 and corresponding U.S. Pat. No.5,833,088, a typical container 12 occupies a volume of approximately 2to 10 ml. It is preferred that the container 12 have a volume that issmaller than 50 ml, preferably smaller than 30 ml, and in particularsmaller than 20 ml. In this way, a compact design of the inhaler 1 andconsumability within the shelf life of the pharmaceutical agentpreparation 4 can be ensured. With respect to the preferred design ofthe container 12, reference can be made in addition to InternationalPatent Application Publication WO 00/49988 A2 and corresponding U.S.Pat. No. 6,988,496.

The container 12 is preferably designed essentially cylindrical or likea cartridge, and preferably, is securely integrated in the inhaler 1, inparticular so that removal or replacement of the container 12 isimpossible or at least is not possible without destroying or damagingit. It is thus preferred that the inhaler 1 is a disposable orthrow-away product. However, other configurations are also possible.

The container 12 is preferably designed in a rigid manner, in particularwhereby the pharmaceutical agent preparation 4 is taken up in acollapsible bag 13 in the container 12.

The inhaler 1 can preferably have a device for the forcing aeration ofthe container 12. In particular, in the case of initial tensioning,base-side tapping or opening of the container 12 is done. In particular,a spring 15 with axial action arranged in a housing 14 of the inhaler 1comes to rest on the container base 16, which with a tapping element 17taps the container 12 or a base-side, in particular gas-tight, seal thefirst time it is put in place for aeration.

Here, the device for the forced aeration is thus formed by the tappingelement 17, which is held or formed by the spring 15. The tappingelement 17 can also be realized without the spring 15. However, otherdesign solutions are also possible.

It is noted that only the outside shell of the container 12 is opened inthe tapping or in the aeration. The bag 13 remains preferably undamagedduring the forced aeration. In the discharge of the pharmaceutical agentpreparation 4 from the bag 13, the bag 13 can collapse, and for pressureequalization, ambient air 18 can flow back into the container 12 via theaeration or tapping opening.

Before the inhaler 1 is used for the first time, a preferably repeatedtensioning and triggering of the inhaler 1 is performed. By thisso-called priming, any air present is displaced from the pharmaceuticalagent preparation 4 into a delivery tube 19 and into a pressuregenerator 20 and then into the discharge nozzle 2. Then, the inhaler 1is ready for inhalation.

The amount of pharmaceutical agent preparation 4 delivered per stroke orper spraying process is preferably approximately 10 μl to 50 μl inparticular approximately 10 μl to 20 μl, and quite preferablyapproximately 15 μl.

A tensioning device 21, preferably a mainspring, is preferablyintegrated pre-tensioned in order to achieve a high delivery pressure.In the inhaler 1 according to the invention, the pressurization anddelivery of the pharmaceutical agent preparation 4 during the sprayingprocess are preferably produced only by energy stored in the tensioningdevice 21, in particular spring force. The inhaler 1 is thus preferablydesigned in that forming of an aerosol is independent of a tensioningprocess, even if prior tensioning can be a requirement for the formingof aerosol 3. Preferably, the inhaler 1 is designed in such a way thatforming of aerosol—in particular the dose, the discharge rate and/or thedischarge speed—is not affected independently of the tensioning processor by the tensioning process. In this way, a reliable metering can beachieved.

The inhaler 1 is preferably designed in such a way that thepharmaceutical agent preparation 4 in the pressure generator 20 in apressure chamber 22 reaches a pressure of 5 MPa to 60 MPa, in particular10 MPa to 50 MPa, in the dispensing. In the dispensing or spraying ofthe pharmaceutical agent preparation 4, a pressure of approximately 50MPa to 60 MPa, in particular approximately 10 MPa to 30 MPa, isespecially preferably reached at the discharge nozzle 2 or its nozzleopenings. The pharmaceutical agent preparation 4 is then converted intothe aerosol 3, whose droplets have an aerodynamic diameter of up to 20μm, preferably approximately 3 μm to 10 μm. The spraying action or thespraying effect is realized or further supported by preferablyintersecting streams, which are dispensed by the discharge nozzle 2.

The inhaler 1 is preferably designed in such a way that the aerosol 3 isdispensed at low speed, in particular at a speed of less than 2 m/s,especially approximately 1.6 m/s or less (in each case measured at a10-cm interval from the discharge nozzle 2). The inhaler 1 is thuspreferably designed as an SMI. The low dispensing speed can be realizedor supported in particular by intersecting jets of the pharmaceuticalagent preparation 4, which are dispensed into the discharge nozzle 2,and/or corresponding selection of the spring force of the tensioningdevice 21.

The inhaler 1 is especially preferably designed in such a way that theproduction of aerosol in each case lasts over 0.7 s, preferablyessentially 1 s or longer, in particular over 1.5 s. The time period forspraying a dose or in the case of an actuation of the inhaler 1 is thuspreferably over 0.75 s, in particular approximately 1 s or more.

The inhaler 1 also has a delivery device or a pressure generator 20 forconveying and spraying the pharmaceutical agent preparation 4, inparticular in each case in a predetermined, optionally adjustablemetered amount or for metered or meterable spraying. The inhaler 1 canthus administer the pharmaceutical agent preparation 4 in multipledefined doses, preferably as an aerosol 3. Preferably, in each case, adose can be administered with an actuation of the inhaler 1.

The inhaler 1 or pressure generator 20 is designed in particular in sucha way that the delivery, pressure generation and/or spraying is/are donewithout propellant, mechanically, and/or by the energy or force of anenergy reservoir, in particular a spring loader, especially preferablyby the spring force, in the illustrated embodiment by a mainspring,spiral spring or another tensioning device 21. However, other designsolutions are also possible. In this case, it is preferred that thespraying be done independently of a manual operation, in particularindependently of the speed of an actuation of the inhaler 1 or drivenexclusively by the energy stored in the tensioning device 21.

The inhaler 1 or pressure generator 20 comprises a pump device 24,preferably with a holder 25 for the container 12 and/or with a deliveryelement, preferably with the delivery tube 19 designed as a capillaryand with an optional valve, in particular a non-return valve 23. Thepump device 24 is thus preferably an assembly of the pressure generator20, which has the delivery tube 19 and means for its movement.

The pressure generator 20 can also have the pressure chamber 22 and/orthe discharge nozzle 2, in particular in a transition area to thechamber 6.

The pump device 24 can be movable or drivable, in particular by thetensioning device 21. It is preferred that the pump device 24 fordischarging the pharmaceutical agent preparation 4 be drivableexclusively by the tensioning device 21.

The container 12 is attached in the inhaler 1 via the holder 25, inparticular in a clamping or resting manner, so that the delivery tube 19plunges into the container 12. In this case, the holder 25 can bedesigned in such a way that the container 12 can be attachedpermanently, preferably in a resting manner.

The inhaler 1 comprises an actuating lever 26 for preferably axialtensioning of the tensioning device 21. When the tensioning device 21 istensioned, the pump device 24 is preferably moved with the container 12,downward in the illustrated embodiment, and the pharmaceutical agentpreparation 4—more precisely, the next dose—is suctioned off from thecontainer 12 into the pressure chamber 22 of the pressure generator 20via the non-return valve 23.

During subsequent depressurization of the tensioning device 21, inparticular after actuation of a triggering device 27, the pharmaceuticalagent preparation 4 is tensioned in the pressure chamber 22. To thisend, the pump device 24 or the delivery tube 19 can be moved upwardagain in the case of the now-closed non-return valve 23 bydepressurization of the tensioning device 21 and can now act as aplunger. Preferably, to this end, the pump device 24 is shifted linearlyor axially with the delivery tube 19, in particular only by thetensioning device 21. This pressure expels the pharmaceutical agentpreparation 4 through the discharge nozzle 2, whereby it is formed intothe preferably respirable aerosol 3, as indicated in FIGS. 1 and 2.

FIGS. 4 and 5 show sections of the inhaler 1, according to theinvention, with the tensioning mechanism 28 for tensioning thetensioning device 21, whereby the actuating lever 26 is shown in FIG. 4in its rest position and in FIG. 5 in the tensioned position. In thetensioned position of the actuating lever 26, the tensioning device 21is tensioned; in the rest position the tensioning device 21 isuntensioned, i.e., relaxed, or only pre-tensioned.

In the variant embodiment shown, the inhaler 1 is designed so that itcan be tensioned and/or triggered with one hand. This section is offsetparallel to the longitudinal axis in order to show elements of thetensioning mechanism 28 that are arranged laterally to the dischargenozzle 2 and the pump device 24.

According to an aspect of this invention that can also be achievedindependently, the tensioning mechanism 28 has a lever gear 29 fortensioning the tensioning device 21.

The pump device 24 and/or holder 25 is/are preferably axially movable bythe lever gear 29. To this end, the pump device 24 and/or holder 25 canbe guided axially, in particular by a cam or arm that is guided in alink. However, other solutions are also possible.

Furthermore, it is preferred that the pump device 24 and/or holder 25 bemounted in a manner that is stationary or kept from rotating. In thisway, the tensioning mechanism 28 advantageously can be separatedtemporarily from the pump device 24 and/or holder 25 and coupled again.

The tensioning device 21 is designed to convey the pharmaceutical agentpreparation 4 from the discharge nozzle 2 in a movement of the pumpdevice 24 that is caused by the tensioning device 21. To this end, thepressure generator 20 can pressurize and/or spray the pharmaceuticalagent preparation 4 by energy stored in the tensioning device 21.

Below, the lever gear 29 is first described functionally based on thelever arms and then described spatially based on the elements forminglever arms, since both the concept and the design also can be achievedindependently and have advantageous aspects of this invention that canalso be combined with one another since function and implementationcomplement one another.

The lever gear 29 especially preferably comprises an elbow lever 30. Theelbow lever 30 has two lever arms 32, 33 that are connected to oneanother by a joint 31 (elbow) and that are also mounted in a hingedmanner on the ends facing away from the common joint 31. If a force F′acts on the joint 31 of the elbow lever 30 perpendicular to theconnecting line 34 of its outer end point, forces F″ are realized on theends in the direction of the connecting line, and said forces are allthe greater the smaller the angle α between the connecting line andlever. In particular, the force ratio is F″=F′/(2 tan α). Withincreasing extension, i.e., the smaller the angle α, the greater thegear reduction and thus the lever action of the elbow lever 30 are.

Preferably, the lever arms 32, 33 are at least essentially equally long,in particular more than 20 mm or 25 mm and/or less than 35 mm or 30 mm.

Furthermore, it is preferred that the lever gear 29 have at least twolevers designed for gear reduction, preferably with an elbow lever 30and a one-sided lever 35. The elbow lever 30 can be driven by means ofthe one-sided lever 35.

The one-sided lever 35 can be hinged on one end and can be loaded with aforce F on another end. The one-sided lever 35 can have a shorter leverarm 36 with a length r1 and a longer lever arm 37 with a length r2,whereby the shorter lever arm 36 can correspond to the first lever arm32 of the elbow lever 30. The force ratio under the assumption ofperpendicular forces with force F acting on the end point of the secondlever arm 33, facing away from the pivot point, for example by manualactuation, is F′=F*r2/r1. The length of the longer lever arm 37preferably corresponds to more than twice, in particular more than threetimes, the length of the shorter lever arm 36.

Even if the indicated formulas because of the assumption ofperpendicular forces only represent approximations and forceparallelograms could be used to ensure more precise treatment, it isclear from the basic treatment that the levers 30, 35 in each caseproduce a gear reduction or force multiplication; the lever gear 29 isthus designed in multiple stages, in particular reduced in multiplestages. The lever gear 29, however, can also be designed in multiplestages in another way, in particular reduced in multiple stages.

The lever gear 29 offers the advantage that the lever action or gearreduction increases in the course of the tensioning process, inparticular at the end of the tensioning process. In this way, it can beachieved that in the case of a manual actuation, the tensioning processis reliably performed until the end. Thus, a reliable metering can beachieved.

The lever gear 29 preferably comprises the actuating lever 26 and an arm38, which can form the elbow lever 30 and/or the additional, preferablyone-sided lever 35.

The actuating lever 26 can be hinged with a first end 39 at a housing 14of the inhaler 1. The housing 14 can be designed in multiple parts. Inthis way, it can be provided that the actuating lever 26 is hinged on ahousing part, which has at least one receptacle for the pump device 24or the pressure generator 20 and/or whereby the housing part is designedwith the actuating lever 26 to be taken up in a housing part of thehousing 14 that forms a gripping area or handle. Preferably, the housingparts can be connected to one another in a resting manner and/or can beinserted into one another. The actuating lever 26 is especiallypreferably hinged at least on a housing part that holds the tensioningdevice 21, and it houses and/or forms a stop for the tensioning device21. In this way, it can be ensured that forces generated by means of theactuating lever 26 can be introduced into the tensioning device 21.Other solutions are also possible, however, for example whereby thehousing 14 can also be formed in one piece, in particular in one piecewith the chamber 6 and/or with the dispensing device 7.

The actuating lever 26 preferably comprises an actuating section 40, inparticular a gripping area, on an area facing away from the first end 39or a pivot point 41 with the housing 14 or is designed in another wayfor manual actuation.

The actuating lever 26 can have a pressure position and a rest position.Preferably, the actuating lever 26 can pivot between the pressureposition and the rest position.

In the pressure position, the actuating lever 26 can be brought up tothe housing 14 of the inhaler 1, can rest against the housing 14 and/orbe oriented at least essentially parallel to the housing section 38adjacent to the actuating lever 26. The housing section 42 can form ahandle or a grip. In the rest position, the actuating lever 26preferably projects from the housing 14 or housing section 42. In thiscase, it can be provided that the actuating lever 26 at its pivot point41 has a preferably hinge-like joint and/or rests against the housing14, at an increasing distance from the pivot point 41, but arrangedfurther removed from the housing 14, i.e., is swung away from thehousing 14.

In the illustrated example, the actuating lever 26 can be pivoted aroundthe pivot point 41, preferably by at least 10°, in particular at least15°, and/or less than 25°, in particular less than 21°. However, otherdesign solutions are also possible.

The actuating lever 26 can be arranged with the first end 39 in thehousing 14, can be aligned to the housing 14, or can be mounted to pivotin the housing 14, in particular housing section 42. In this case, thehousing section 42 can form a stop 43 for the actuating lever 26. Thestop 43 preferably limits the pivoting angle of the actuating lever 26,in particular to make possible the above-mentioned pivoting areas.

By the arrangement of the actuating lever 26 with the first end 39 inthe housing section 42, sections of the actuating lever 26 and thehousing 14 that are movable against one another in a shearing way canadvantageously be avoided, ensuring that the danger of injury bypinching can be reduced.

The arm 38 of the lever gear 29 is preferably hinged on the actuatinglever 26. The arm 38 can be designed to connect the actuating lever 26to the pump device 24. To this end, the arm 38 can be hinged on theactuating lever 26 on one side at a pivot point 44, which preferablycorresponds to the joint 31 that is especially hinge-like, and on asecond end that faces away from the pivot point 44, the arm 38 can bedesigned to introduce force into the tensioning device 21, ensuring thatthe tensioning device 21 can be tensioned. To this end, the arm 38 canbe mounted to rotate on the pump device 24, the holder 19, or thetensioning device 21. However, alternative solutions are alsoconceivable, in which the tensioning device 21 can be tensioned via alever gear 29.

The actuating lever 26 together with the arm 38 preferably forms theelbow lever 30. The latter is securely hinged preferably only on one endin the pivot point 41. The elbow lever 30 is driven or actuated in sucha way that the pivot point 41 of the actuating lever 26 is shifted withthe arm 38, ensuring that the pump device 24 preferably can moveaxially. To this end, the pump device 24 is preferably mounted axially.Furthermore, it is preferred that the pump device 24 be secured againstrotating around the longitudinal axis L.

By the lever characteristic of the elbow lever 30, it is achieved thatin the movement of the actuating lever 26 in the direction of thetensioned position, the force that is to be applied is reduced. As aresult, the effect of this is that an actuation of the tensioningmechanism 28 during the course of the tensioning process at least in anarea before the completion of the tensioning process requires a smallerforce on the actuating lever 26. In the last section, this conveys thesensation that the actuating lever 26 almost moves by itself, becausepreviously, greater force was necessary. Advantageously, the effect ofthis is that the actuating lever 26 is always swung into the pressureposition.

The elbow lever 30 preferably forms a pressure point. The pressure pointis characterized by a peak force in the pressurization plot orpressurization process. In the rest position, the elbow lever 30 isstill comparatively far removed from the extension. The gear reductionis thus comparatively small. In a first section of the tensioningprocess, starting from the rest position of the actuating lever 26, thegear reduction by the elbow lever 30 is less greatly reduced than theincrease in force by the increasing tensioning of the tensioning device21. Consequently, the force that is to be applied with the actuatinglever 26 for the tensioning process increases in an area starting fromthe rest position. By the nonlinear development of the gear reduction ofthe elbow lever 30, the active tensioning force increasing by thetensioning device 21 is then overcompensated. In the tensioning process,a maximum of the force to be exerted on the actuating lever 26 for thetensioning process is therefore developed. After exceeding the maximum,the necessary force for further tensioning the tensioning device 21 islower because of the increasing extension of the elbow lever 30.Alternatively or additionally, the pressure point can be realized usinga guiding surface with variable gradient or a screw or worm drive withvariable screw lead.

Because of the comparatively low force that must be exerted in the lastsection of the pivoting of the actuating lever 26 from the pressureposition to the actuating lever 26, it can be ensured that the actuatinglever 26 usually reaches the pressure position. In this way, areproducible and unchanged metering can be achieved.

It is preferred that the arm 38 be hinged to the actuating lever 26between the pivot point 41 and the actuating section 40. In this way,the additional one-sided lever 35 is realized. The use of an elbow lever30, in which the actuating section 40 acts directly on the pivot point44 of the actuating lever 26 with the arm 38, is also possible as analternative, however. The elbow lever 30 can thus also be realizedwithout the one-sided lever 35, and it can be used as a tensioningmechanism 28.

The arm 38 is preferably designed to be L-shaped and/or in the manner ofa fork. In this way, the arm 38 can encompass the delivery tube 19. Inthis way, the force exerted by the lever gear 29 can be introduceduniformly, in particular via the pump device 24, into the tensioningdevice 21. In this connection, the L shape helps to minimize themovement space for the elbow lever 30. In particular, the arm 38 isformed forklike or as a tensioning fork, whereby two preferably L-shapedsections are connected by an arm, whereby the arm is a joint and/or theends of the sections facing away from the arm are designed forintroducing force into the tensioning device 21. In this way, thehousing volume can be minimized. As an alternative or in addition, thearm 38 can have an arc shape or the like.

The arm 38 preferably comprises polycarbonate (PC), polyoxymethylene(POM) and/or polybutylene terephthalate (PBT) or is formed therefrom,preferably reinforced, in particular glass-fiber-reinforced. The forkshape of the arm 38 in connection with the high forces, which occur inthe tensioning of the tensioning device 21, results in specialrequirements on the stability of the material being used. Here, theproduction at least of the arm 38 made of the above-mentioned materialshas turned out to be especially advantageous, surprisingly enough.

The pump device 24 preferably comprises a receptacle 45, a stop or anopposing bearing for rotatable mounting of the arm 38. In this way, theforce can be transferred from the lever gear 29 to the pump device 24.

Preferably, the tensioning mechanism 28 is thus designed to mount thearm 38 in a tensioning movement of the lever gear 29 on the pump device24 in such a way that a force from the lever gear 29 can be introducedinto the tensioning device 21. As an alternative or in addition, the arm38 can be detachable in a movement of the actuating lever 26 in thedirection of the rest position of the pump device 24. It can thus beprovided that the tensioning mechanism 28 or the lever gear 29 can bedetached completely from the pump device 24. This advantageously allowsa movement of the pump device 24 for administering fluid only by meansof the force by the tensioning device 21. In this way, a reproduciblemetering and formation of aerosol can be ensured. The receptacle 45 ispreferably mounted in a manner that is stationary, in particularrelative to the longitudinal axis L. In this way, it is ensured that atensioning mechanism 28 that is triggered by the pump device 24 can belater taken up again by the receptacle 45.

The inhaler according to the invention preferably comprises thetriggering device 27, which is designed—when the tensioning process iscompleted—to secure the tensioning device 21 and/or the pump device 24preferably snugly against movement. Furthermore, the triggering device27 can be designed, in particular in the case of manual actuation, tomake possible, in particular to trigger, a movement of the pump device24 caused by the tensioning device 21. The triggering device 27 is thuspreferably designed to block the forming of aerosol and to release it inthe activation.

The housing 14, in particular the housing section 42, in particular agripping area of the housing 14, can have, carry and/or encase thepressure generator 20, the pump device 24, and/or the tensioning device21.

The tensioning mechanism 28 is preferably designed for conversion of arotational movement, in particular a pivoting movement, of the actuatinglever 26 in a linear tensioning movement that is axial here. However,other design solutions are also possible.

A pivoting movement in terms of this invention is preferably arotational movement or a movement rotating around a pivot axis, which islimited in the freedom of movement in such a way that no completerotation is possible. In particular, a pivoting movement in terms ofthis invention is a rotational movement, which is limited in design,preferably to less than 180°, in particular less than 90°.

The tensioning mechanism 28 is designed for tensioning the tensioningdevice 21. To this end, the tensioning mechanism 28 can turn atensioning movement, in particular a pivoting movement, into a linear oraxial movement in order to move the pump device 24 or the holder 25 viasuch a movement and/or to compress—and in this way, to pressurize—thetensioning device 21.

To tensioning the tensioning device 21, the pump device 24 can thus bemoved by means of the tensioning mechanism 28 preferably axially, inparticular along the longitudinal axis L. To this end, the pump device24 or the holder 25 can be guided axially. By the axial movement, aforce can be exerted on the tensioning device 21 in order to storeenergy in the tensioning device 21 by compression.

At the end of the tensioning process, the triggering device 27 canpreferably automatically and/or by friction and/or by overlapping blocka movement of the pump device 24 induced by the tensioning device 21. Byactivation of the triggering device 27, in particular by movementagainst a movement ensuring that the triggering device 27 blocks thepump device 24 against movement, the movement of the pump device 24 canbe released, and the pump device 24 can be moved or driven by means ofthe tensioning device 21. In this case, the aerosol 3 can be formed fromthe pharmaceutical agent preparation 4 as described above.

The triggering device 27 can optionally be secured with a triggeringblocker 46 against the triggering of the releasing of aerosol. Inparticular, with completion of the tensioning process or with blockingby the triggering device 27, the triggering blocker 46 can automaticallysecure the triggering device 27 against triggering. It is preferred thatthe triggering blocker 46 automatically releases the triggering device27 as soon as the actuating lever 26 has again reached its restposition. Then, the triggering device 27 can be actuated, for examplemanually, in particular by actuating an actuating element 56, inparticular a button, or automatically.

The triggering device 27 can be activated or actuated automatically whenreaching the tensioned position and/or when the actuating lever 26 againreaches its rest position. In particular, the triggering by thetriggering device 27 comprises a release of the pump device 24, so thatthe pump device 24 can be moved by the tensioning device 21 and in thisway the aerosol 3 can be realized.

In a preferred embodiment, the triggering device 27 has a triggeringdelay or other device that produces a delay on the part of the pumpdevice 24 relative to the actuating lever 26 moving into the restposition. In this way, it can be ensured that even without an actuatingelement 56, triggering and releasing of aerosol is made possible in areliable way and with a reproducible dose.

For example, a means is provided that makes possible a fully automatictriggering after the actuating lever 26 has left its tensioned position.In particular, the triggering is done after the actuating lever 26 hasbeen swiveled away from its tensioned position or from a position thatfaces the housing 14 by at least 1°, preferably at least 2°, and inparticular at least 3°. In this way, an automatic triggering can beachieved with a pressure generator 20 that makes the tensioningmechanism 28 lag or a pump device 24 that makes the tensioning mechanism28 lag. In addition to the reliable metering, this offers the advantagethat a triggering with a very small delay is made possible by a userdisengaging the actuating lever 26. However, other solutions are alsopossible, for example a triggering without a delay. In this case, theactuating lever 26 is preferably moved back at sufficient speed into therest position, so that the tensioning mechanism 28 does not affect theforming of aerosol, in particular whereby a movement of the pump device24 makes the movement of the tensioning mechanism 28 lag. It ispreferred that the pump device 24 can be moved for the forming ofaerosol without contact with or under the influence of the tensioningdevice.

In one method, the inhaler 1 can be tensioned via the elbow lever 30,whereby the elbow lever 30 acts on the tensioning device 21 andpreferably compresses the latter axially.

The actuating lever 26 can have a reset element 47 such as a spring,which is designed to move the actuating lever 26 into its rest positionor to hold it there. In principle, the tensioning device 21 can bringthe actuating lever 26 back into the rest position via the tensioningmechanism 28. It is preferred, however, that after the tensioningprocess, the tensioning mechanism 28 be completely detached from thepump device 24, so that the pump device 24 can be moved independently ofthe tensioning mechanism 28 by the tensioning device 21. Therefore, itis preferred that a reset element 47, independent of the tensioningdevice 21, be provided, for example a spring, a rubber seal, or thelike, acting on the actuating lever 26 in the direction of the resetposition.

A pivot axis of the actuating lever 26 at the pivot point 41 can bearranged crosswise and spatially offset relative to the longitudinalaxis L of the inhaler, in particular an axis that corresponds to thedirection of movement of the pump device 24 and/or the dischargedirection of the discharge nozzle 2. In this way, it can be achievedthat the pivot point 41 of the actuating lever 26 with the housing 14does not impede the flow of the aerosol 3. Furthermore, in the spatiallyoffset arrangement of the pivot point 41 relative to the longitudinalaxis L, the elbow lever 30 can be operated closer to its extension,i.e., with a greater lever action.

According to another aspect of this invention that can also be achievedindependently, the inhaler 1 is designed for metered spraying of thepharmaceutical agent preparation 4 and has an indicator 48, which has ametering ring 50, mounted to rotate around an axis of rotation 49, withindicator means 51 for displaying a number of still available or alreadyadministered doses, in particular, i.e., a dose indicator.

In a perspective view, FIGS. 6 and 7 show essential parts of theindicator 48 with and without the pressure generator 20.

The metering ring 50 preferably comprises a preferably axial throughpassage 52. The through passage 52 can be arranged and designed in sucha way that the pressure generator 20 or parts thereof, in particular thepump device 24, can be arranged in the through passage 52. The meteringring 50 can thus be arranged around the pressure generator 20 or thepump device 24.

The metering ring 50 can be guided in a groove or link. As analternative or in addition, other guide means, in particular at leastthree, preferably at least four, guide arms 53 can be provided, whichare mounted to rotate the metering ring 50 and/or to prevent a lateralor axial movement.

As indicator means 51, for example, the metering ring 50 can haveimprinted dashes, numbers which identify the number of does that arestill available or have already been administered. The indicator means51 are preferably applied to a radial front side. As an alternative orin addition, the metering ring 50 can also have—as an indicator means51—a color indicator, for example a marking or a marked area, which cancorrespond to a remaining volume of the pharmaceutical agent preparation4, in particular to display an inventory. Different indicator means 51can furthermore be combined; for example, the same metering ring 50 caninclude still available or already administered doses, dashes to displayin each case a dose consisting of multiple triggerings and/or a colored,for example, red, marked area, which can warn of a reduced remainingamount of the pharmaceutical agent preparation 4. However, othersolutions are also possible.

The inhaler 1, in particular the housing 14, can have a window 54 forvisibility of the metering ring 50 arranged in the inhaler 1 (cf. alsoFIG. 1).

According to an aspect of this invention that can also be achievedindependently, the metering ring 50 can be moved or rotated by thetriggering device 27. The triggering device 27 can be assigned to thepressure generator 20, in particular whereby the triggering device 27can block and/or release the pressure generator 20. The pressuregenerator 20 is especially preferably designed or works mechanically asa pump. The same triggering device 27 can be used for driving themetering ring 50.

According to another aspect of this invention that can also be achievedindependently, the inhaler 1, in particular the triggering device 27,has a pivot arm 55, whereby the metering ring 50 can be moved or rotatedby pivoting the pivot arm 55. In particular, the pivot arm 55 isdesigned as a blocking ring or section of a blocking ring for blockingand releasing the pressure generator 20.

It is preferred that, by means of the pivoting movement of the pivot arm55, the metering ring 50 be driven in order to have the display trackthe number of still available or already dispensed doses in preferablyeach individual triggering of the inhaler 1. In particular, the sprayingby the triggering device 27 or by pivoting the pivot arm 55 can bereleased, and the metering ring 50 can be driven simultaneously and/orwith the same movement by the triggering device 27 and/or by pivotingthe pivot arm 55.

In the illustrated embodiment, the triggering device 27 has an actuatingelement 56, in particular a snap fastener, for manual triggering of theforming of aerosol. The actuating element 56 can drive the pivot arm 55.In particular, the actuating element 56 is formed in one piece with thepivot arm 55 or in another way is coupled to the latter. However, othersolutions are also possible.

The metering ring 50 can be transported with release of the pump device24 or the tensioning device 21. Then, the tensioning device 21 istensioned again with the tensioning mechanism 28. As an alternative orin addition, the metering ring 50 is driven in—or by—locking or pivotingof the pivot arm 55.

When the tensioning process is completed, the pivot arm 55 can form apositive fit with a positive device 57 of the pressure generator 20 orthe pump device 24, ensuring that the pressure generator 20 or the pumpdevice 24 is blocked against triggering or the forming of aerosol. Inparticular, it is provided that the pivot arm 55 overlaps a part of thepump device 24, in particular the holder 25, by pivoting and herewithprevents the movement of the pump. In particular, the holder 25 or anedge of the holder 25 therefore forms the positive device 57. However,other solutions are also possible.

The pivot arm 55 can be pre-tensioned against the positive device 57,preferably against the pump device 24, in particular against the holder25, so that the pivot arm 55 can secure the pressure generator 20automatically against triggering by friction when the tensioning processis completed. In the illustrated embodiment, the pivot arm 55 is clampedin particular by means of a spring against the pump device 24. At theend of the tensioning process, the pivot arm 55 reaches the couplingdevice 60, in particular an upper edge, recess, or the like, of the pumpdevice 24, preferably automatically swings laterally over the edge, intothe recess, or in another way forms a positive fit, which prevents anaxial pump movement of the pump device 24.

By pivoting the pivot arm 55, in particular by locking the pump device24, a drive of the metering ring 50 can be prepared, so that themetering ring 50 can be rotated (again) with triggering.

It is preferred that the actuating lever 26 be longer than 10 cm,preferably longer than 12 cm, in particular longer than 14 cm and/orshorter than 20 cm, preferably shorter than 18 cm, and in particularshorter than 16 cm, and/or can be swiveled by more than 5°, preferablymore than 10°, in particular more than 15° and/or less than 45°,preferably less than 40°, and in particular less than 35°.

Relative to the pivoting movement of the pivot arm 55, reference is madeto the definition given above.

The inhaler 1 preferably comprises a non-return device 58, which blocksa rotation of the metering ring 50 in one direction and/or allows arotation of the metering ring 50 only in a direction of rotation.

To drive the metering ring 50, the triggering device 27, in particularthe pivot arm 55, has a drive device 59, which is designed to rotate themetering ring 50, preferably by pivoting the pivot arm 55.

The metering ring 50 can have a coupling device 60 for driving themetering ring 50 by the drive device 59, in particular a drive track ora positive device, preferably a gear. In the illustrated embodiment, thecoupling device 60 is formed on a front surface and/or by a gear, inparticular with asymmetrical tooth flanks. The drive device 59 can bedesigned to engage in the coupling device 60 of the metering ring 50.

Preferably, the drive device 59 comprises a carrier, a detent pawl, atongue, or the like or is designed as a carrier, detent pawl or tongue.In particular, the drive device 59 is flexible, bendable, and/or has anedge for engagement in the coupling device 60 or gear for driving themetering ring 50. In this case, it can be provided that the drive device59 engages in the gear in the movement of the pivot arm 55 in thetensioning direction or in releasing or triggering direction, and inthis way drives the metering ring 50.

The pivot arm 55 can pivot preferably more than 2°, in particular morethan 4°, and/or less than 45°, preferably less than 30°, in particularless than 20°, and in the illustrated embodiment approximately 5° to10°.

During a tensioning process, in particular when the pivot arm 55 isswung in order to block the pressure generator 20 or during a triggeringprocess when the pivot arm 55 is swiveled in order to release thepressure generator 20, the drive device 59 can engage with the couplingdevice 60 and can be moved via or relative to the coupling device 60. Inthis way, the drive device 59 can be moved into a position in which thedrive device 59 can be coupled at another point in the coupling device60, in particular in the next or another tooth of the gear. Thus, themetering ring 50 can be rotated successively, preferably triggering fortriggering, in each case by at least essentially the same angle. It ispreferred that the drive device 59 and the coupling device 60 bedesigned and arranged relative to one another so that the drive device59 drives the coupling device 60 in one direction and can be shifted inthe opposite direction relative to the coupling device 60.

The coupling device 60 is preferably provided on a front side of themetering ring 50, and the indicator means 51 is provided on an outerperipheral surface of the metering ring 50.

It is preferred that the angle of rotation of the metering ring 50 bebetween 0.5° and 1.5° per triggering. In this way, on the one hand, aprecise enough display can be achieved, and, on the other hand, asufficient number of doses that can be metered can be achieved.Preferably, the metering ring 50 is designed to indicate more than 120,preferably more than 150, and/or less than 250, preferably less than220, and in particular approximately 180 doses.

A characteristic of this solution is that the drive device 59 can bemoved preferably by pivoting the pivot arm 55 around a first axis ofrotation 61 on a driving means track 62. Furthermore, the couplingdevice 60 of the metering ring 50 can be moved around a second axis ofrotation 63 on a metering ring track 64. It is especially preferred thatthe driving means track 62 and the metering ring track 64, indicated inFIGS. 6 and 7 by arrows, be different. In particular, the driving meanstrack 62 and the metering ring track 64 intersect, preferably only once.Also, the position of the axes of rotation 61, 63 can be different. Inparticular, the first axis of rotation 61 of the driving means 62 lieswithin the metering ring track 64 or the metering ring 50. Furthermore,the driving means track 62 and the metering ring track 64 can havedifferent radii. It is preferred that the first axis of rotation 61 andthe second axis of rotation 63 be arranged at least essentially parallelto one another or point spatially in the same direction.

The drive device 59 can preferably be rigidly connected and/or formedintegrally with the blocker ring 55 via an arm.

The drive device 59 and the corresponding coupling device 60 arepreferably formed by a gearwheel and detent pawl. As an alternative orin addition, however, this can also be a friction means and/or afriction track, whereby the drive device 59 forms a frictionalconnection with the coupling device 60 for driving the metering ring 50.In this case, the non-return device 58 can also prevent a back-and-forthmovement of the metering ring 50. In this way, a continuous meteringmovement of the metering ring 50 can thus be ensured. However, othersolutions are also possible.

The drive device 59, however, especially preferably comprises a detentpawl or another carrier, and the coupling device 60 comprises anespecially asymmetrical gear. In this connection, it is preferred thatthe drive device 59 have a guide surface 65, which is designed to rotatethe metering ring 50 by moving the guide surface 65 along the couplingdevice 60, in particular the gear, of the metering ring 50. In this way,a pivoting of the pivot arm 55 can be implemented especially effectivelyin a rotational movement of the metering ring 50.

The guide surface 65 can be inclined relative to a tangent to thedriving means track 62, preferably so that the movement of the guidesurface 65 makes possible an advancing of the metering ring 50. Inparticular, the guide surface 65 moves the metering ring 50 by means ofa tooth of the coupling device 60 with a movement of the drive device 59with the guide surface 65, which removes the drive device 59 from thesecond axis of rotation 63 of the metering ring 50. However, otherdesign solutions are also possible.

The drive device 59 can be pre-tensioned against the coupling device 60.With this, it can be achieved that the drive device 59 can slide overthe coupling device 60 when moving in a direction blocked by thenon-return device 58 and can drive the metering ring 50 again to achanged position. To this end, the drive device 59 can be spring-loadedor elastically deformable. Furthermore, it is preferred that the drivedevice 59 be tongue-shaped, elongated and/or flat. In this way, apre-tensioning can be realized especially easily and effectively, whichensures a secure drive and at the same time supplies the elasticity thatprompts the drive device 59 to move toward the rotational directionrelative to the coupling device 60.

The drive device 59 is preferably fastened to the pivot arm 55,molded-on and/or formed in one piece with the pivot arm 55. However,other solutions are also possible. In particular, the drive device 59can also be shifted only laterally in order to drive the metering ring50. In this case, it is preferred in addition that the metering ringtrack 64 and the now straight drive means track 62 intersect. Inparticular, the guide surface 65 can be designed in such a way thatguiding of the guide surface 65 along the coupling device 60 makespossible a drive of the metering ring 50. However, still other designsolutions are also conceivable.

As a whole, this invention can make possible the drive of an indicatorfor displaying a number of still available or already administereddoses, in particular the metering ring 50 by pivoting the pivot arm 55and/or by triggering the pressure generator 20.

In a possible alternative, the pivot arm 55 is not provided for lockingthe pump device 24 and/or for triggering the forming of aerosol. Thepivot arm 55 is thus not necessarily part of the triggering device 27,but rather it can also be used independently of the triggering device 27for driving the indicator 48. Moreover, other indicators that are notnecessarily operated with a metering ring 50 can also be driven by thepivot arm 55 according to the invention. In particular, the meteringring 50 can also be a metering ring 50 that is formed to be onlypartially annular. As an alternative or in addition, metering rods,metering gauges, in particular on an unwinding roller or the like, orother carriers can be used for the indicator means 51, which also aredriven by means of the pivot arm 55. However, the depicted combinationof metering ring 50 and drive device 59 is especially preferred.

The metering ring 50 can have an outside diameter that is larger than 1cm, preferably larger than 1.5 cm, in particular larger than 1.8 cm,and/or smaller than 4 cm, preferably smaller than 3.5 cm, and inparticular smaller than 3 cm. This makes possible a detailed applicationof the indicator means 51, in particular a fine scale.

The indicator means 51 preferably comprises lines, numbers, or the like.It is not necessary that the numbers immediately follow one another. Forexample, the indicator means 51 has numbers in intervals of five or ten.In an alternative, the indicator means 51 comprises a dose scale. Forexample, when using the inhaler 1 in larger animals, a repeatedtriggering may be necessary in order to reach the necessary total dose.In this connection, a dose scale can be used as an indicator means 51,whereby the dose scale in each case comprises breakdowns for a specificnumber of multiple triggerings. For example, the indicator means 51 canhave markings for each fifth, sixth, seventh, eight, ninth or tenthtriggering. Based on the application or patient, the inhaler 1 can thenhave an indicator means 51 that is set up accordingly.

For the inhalation of the aerosol 3 by means of the inhaler 1,preferably an inhalation valve 66 is provided, which is depicted in FIG.8 as an exploded drawing, closed in FIG. 9, and open in FIG. 10. Theinhalation valve 66 comprises a valve element 67, in particular a valveflap or membrane. The valve element 67 is preferably flexible, bendable,flat, thin, disk-like, conical at least in sections and/ormembrane-like. The valve element 67 can have silicone or LSR (liquidsilicone) or be formed therefrom.

The inhalation valve 66 is preferably arranged outside of the chamber 6,but can also form part of the chamber 6.

The inhalation valve 66 is designed for intake of ambient air 18 intothe chamber 6, whereby the inhalation valve 66 is preferably blocked orthrottled in the reverse direction in particular so that in the case ofexhalation, no air and no aerosol from the chamber 6 can be releasedthrough the inhalation valve 66 into the environment. In the illustratedembodiment, the inhalation valve 66 is preferably designed as anon-return valve or membrane-like valve, with or without pre-tensioningin the closed position. However, other design solutions are alsopossible.

According to an aspect of this invention that can also be achievedindependently, the valve element 67 is designed to be annular andcomprises an outer edge 68 and an inner edge 69. The valve element 67 isfastened to the outer edge 68, and the inner edge 69 forms the boundaryof an through passage 70 of the valve element 67. Furthermore, theinhalation valve 66 has a valve body seat 72 for the valve element 67,which corresponds to the inner edge 69.

The inhalation valve 66 is preferably designed so that in the case ofexcess pressure in the chamber 6 relative to the environment or in thecase of a respiratory process in the chamber 6, the inhalation valve 66closes, whereby the valve element 67 rests or is pressed snugly on thevalve body seat 72—cf. FIG. 10. In a respiratory process, the inhalationvalve 66 is opened, and this allows ambient air 18 to flow in throughthe inhalation valve 66 into the chamber 6. To this end, it is providedthat the valve element 67 forms an opening, which makes it possible, bydeforming on its inner edge 69, for the ambient air 18 to flow in.

In the illustrated embodiment, the outer edge 68 of the valve element 67is snugly fastened all the way around. An opening of the inhalationvalve 66 is carried out on the inner edge 69 of the valve element 67.Here, the valve element 67 is lifted from the valve body seat 72 by apressure differential in the flow direction, ensuring that an opening inthe area of the through passage 70 is made. The inhalation valve 66 thuspreferably opens only on the inner edge 69.

The discharge nozzle 2 is preferably arranged in the through passage 70.As an alternative or in addition, the discharge nozzle 2 can be arrangedso that an aerosol 3 released by the discharge nozzle 2 can be releasedthrough the through passage 75 or can be introduced into the chamber 6.

The combination of the aerosol release in the area of the throughpassage 75 or 70 and the opening of the inhalation valve 66 on the inneredge 69 advantageously results in that an air stream that passes throughthe inhalation valve 66 can form a jacket around the aerosol 3, as isknown from, for example, turbofan engines of aircraft for soundinsulation. The concentration of active ingredients is thus preferablyreduced in the edge area of the flow. In this way, it is achieved thatonly comparatively few particles of the pharmaceutical agent preparation4 or the aerosol 3 come into contact with a wall of the chamber 6 or thedispensing device 7 and are deposited. The inhalation valve 66 accordingto the invention thus advantageously results in an especially efficientreleasing of the aerosol 3 with the pharmaceutical agent preparation 4.

According to another aspect of this invention that can also be achievedindependently, the inhaler 1 has a stop 71 for the valve element 67 on aside of the valve element 67 that faces away from the valve body seat72. The stop 71 can prevent an overexpansion and damage of the valveelement 67. As depicted by way of example in FIG. 10, the stop 71furthermore makes it possible, when the valve element 67 is at rest, topre-specify a flow geometry, which in an adequate valve opening is atleast essentially independent of the size of the volume flow, whichpasses through the open inhalation valve 66.

According to another aspect of this invention that can also be achievedindependently, the chamber 6 with the valve element 67 in the openposition forms a closed flow wall 73 and/or nozzle. In particular, it ispreferred that the chamber 6 have the stop 71 that corresponds to theinner edge 69 of the valve element 67, on which the valve element 67rests snugly in the open position, ensuring that the closed flow wall 73is realized. In this way, in an advantageous way, flow detachment, whichwould be associated with the forming of eddies, can be avoided, wherebyeddies can cause particles of the pharmaceutical agent preparation 4from the aerosol 3 to make increased contact with the chamber 6 or toprecipitate in the chamber 6. In particular, it is preferred that thevalve element 67 with the chamber 6 form a nozzle, in particular by aflow cross-section decreasing by means of the valve element 67 in thedirection of flow and then increasing by the chamber 6 in the directionof flow. In this way, in particular a valve nozzle can be realized,ensuring that a forming of aerosol can be supported by the dischargenozzle 2.

The inhalation valve 66 is preferably rotationally symmetrical to thelongitudinal axis L of the inhaler 1 or to a dispensing direction of thedischarge nozzle 2. In this way, a passage of the air flow that isespecially free of eddying is made possible by the inhalation valve 66,thereby reducing the probability that aerosol components will thencondense.

According to another aspect of this invention that can also be achievedindependently, the inhalation valve 66 has a collecting device 74 forsolid and/or liquid substances. The collecting device 74 preferably hasthe valve body seat 72 and/or a receptacle 45 for the discharge nozzle2. The collecting device 74 can have a through passage 75 to accommodatethe discharge nozzle 2 or for the aerosol 3 being run through.

The collecting device 74 can be designed to collect secretions orcondensates, in particular nasal discharges or respiratory condensates,in order to prevent the latter from crusting and blocking the inhalationvalve 66, in particular the valve element 67, and/or the dischargenozzle 2 or an opening of the discharge nozzle 2.

The collecting device 74 can adjoin the valve body seat 72 or form thevalve body seat 72. In the illustrated embodiment, the collecting device74 is formed in the shape of a groove, bowl or shell. In particular, thecollecting device 74 has an annular groove, whose outer edge forms thevalve body seat 72 and/or whose inner edge has a sealing edge or sealinglip 76, which forms the through passage 75, an opening for accommodatingand/or guiding the discharge nozzle 2 through. In one alternative, thevalve body seat 72 can directly form the sealing edge or sealing lip 76for accommodating and/or guiding the discharge nozzle 2 through, inparticular when the inhaler is realized without a collecting device 74.Guiding the discharge nozzle 2 or the aerosol 3 through can also beimplemented in other ways.

In general, it is preferred that the discharge nozzle 2 be taken up inthe inhalation valve 66, be encompassed by the inhalation valve 66,and/or be arranged in the through passage 70 of the valve element 67. Asan alternative or in addition, it is provided that the pharmaceuticalagent preparation 4 or the aerosol 3 is guided through the throughpassage 70 into the chamber 6.

The inhalation valve 66 is designed as a one-way valve or non-returnvalve. To this end, the inhalation valve 66 can make possible aflowing-in of the ambient air 18 through the inhalation valve 66 and/orcan prevent an exiting of air or aerosol 3 through the inhalation valve66.

The opening 70 of the discharge nozzle 2 is preferably arrangeddownstream from the valve body seat 72 and/or a valve plane that isformed by the valve body seat 72. In this way, it can be achieved thatthe aerosol 3 is applied only after passage of the air 18 through theinhalation valve 66, and consequently no aerosol components condense onthe valve element 67.

It is further preferred that the discharge direction of the dischargenozzle 2 be at least essentially identical to a main direction of flowof the air 18 from the inhalation valve 66. In particular, the dischargedirection of the discharge nozzle 2 and the main direction of flow ofthe air 18 from the inhalation valve 66 are parallel and/or coaxial, inparticular relative to the longitudinal axis L. In this way, anespecially efficient aerosol transport is ensured.

The stop 71, preferably formed by the intake opening of the chamber 6,preferably corresponds in shape and diameter to the inner edge 69 of thevalve element 67. In this way, an especially uniform flow wall 73 can beachieved, ensuring that eddies and eddy-induced precipitate of aerosolcomponents can be avoided.

According to an aspect of this invention, the stop 71 is formed by anedge of an intake opening 85 of the chamber 6. This advantageously makespossible continuous flow guidance and flow forming of the air 18 in theflow through the inhalation valve 66 into the chamber 6.

The intake opening 85 of the chamber 6 can have a section that conicallynarrows in the opening direction. The conically-narrowing section ispreferably designed to be free-standing or forms a collar-shapedextension of the chamber 6, which can end in the intake opening 85.

The outer edge 68 of the valve element 67, the inner edge 69 of thevalve element 67, the valve body seat 72, the collecting device 74and/or the stop 71 can be designed at least essentially annular and/orcan be arranged with one another in such a way that the focal points orgeometric foci lie on a common axis, in particular the longitudinal axisL of the inhaler 1. The longitudinal axis L preferably corresponds tothe linear direction of movement of the pump device 24 and/or thedischarge direction of the discharge nozzle 2.

The inhalation valve 66 can have a fastening element 77 forcircumferential fastening of the valve element 67, in particular on itsouter edge 68. The inhalation valve 66 can furthermore have a clampingring 78 for clamping the valve element 67 to the fastening element 77.In particular, the valve element 67 is thus clamped between thefastening element 77 and the clamping ring 78. The valve element 67 canalso, however, be connected preferably snugly with the fastening element77 in another way or can be fastened to the latter, in particular by anadhesive connection. A frictional connection by means of the clampingring 78 is preferred, however.

By the fastening element 77, the clamping ring 78 or in another way, thevalve element 67 can be clamped or pre-tensioned against the valve bodyseat 72. The valve element 67 thus snugly rests in a rest position orwithout the application of force on the valve element 67 preferably onthe valve body seat 72. This can be achieved, on the one hand, byclamping or gripping, as an alternative or in addition also by the shapeor internal stress of the valve element 67 or in another way. In theillustrated embodiment, the inhalation valve 66 is designed withpre-tensioning in the closed position. However, other design solutionsare also possible.

The inhaler 1 can have incoming air openings 79, in particular on theintake side or upstream from the inhalation valve 66. These openings 79make possible a flow of ambient air 18 to the intake side of theinhalation valve 66. In particular, the incoming air openings 79 areformed by through openings of the housing 14.

The fastening element 77, the collecting device 74, and/or the valvebody seat 73 can be connected to one another via at least one arm, inparticular can be formed in one piece.

According to another aspect of this invention that can also be achievedindependently, the inhaler 1 has a respiration indicator 80, which has awall section 81 of a chamber wall 82 that forms the chamber 6 or isformed in this way. In this case, the wall section 81 is designed toindicate a respiratory activity by deforming and/or movement. Inparticular, the respiration indicator 80 is designed to indicate apressure differential between the inside space and the surrounding areaof the chamber 6.

The wall section 81 can be designed to be expandable, flexible,deformable, curved, dome-shaped and/or membrane-like. In this way, it ismade possible that comparatively small pressure differentials also leadto a deforming or movement in order to indicate the respiratoryactivity. In contrast to the chamber 6, the respiration indicator 80 canpreferably be nontransparent, translucent, or opaque. This facilitatesthe reading.

The wall section 81 can be designed to be at least partially deformed inthe shape of a vault or dome or curved in another way under the actionof breathing in, out or through the chamber 6. In this case, a peak 83or vault can be formed, in particular by a pressure differential actingon the wall section 81 between the inside space and surrounding area ofthe chamber 6 and the wall section 81 thus being deformed in acorresponding way.

Under the action of breathing out or through the chamber 6, the peak 83can be facing the inside space of the chamber 6. Starting from a restposition of the wall section 81, a concave deforming is thus formed. Inthis case, it has to be taken into consideration that the chamber 6preferably has rounded walls, a concave deforming of the wall section81, i.e., especially already present if a convex basic shape is at leastpartially compensated for. Especially preferred, however, is a deformingin the intake from or through the chamber 6 or in the case ofunderpressure in the chamber 6 relative to the surrounding area, inwhich as a result, the concave deforming also leads to a concave surfacein the area of the wall section 81.

The wall section 81 is preferably designed in such a way that under theaction of breathing in the chamber 6 or in the case of overpressure inthe chamber 6 relative to the surrounding area, it is convexly deformedor curved or deformed or curved in such a way that the peak 83 is formedon a side facing away from the inside space of the chamber 6. In thiscase, it can be provided that the convex deforming forms in an alreadyconvex basic shape in a rest position or the like of the wall section81, i.e., a convex basic shape is curved in a more convex manner by theconvex deforming.

However, other forms of a deviation of the wall section 81 are alsopossible, which under the action of breathing out or through the chamber6 or in the case of underpressure in the chamber 6 is directed to theinside space of the chamber 6, and/or which under the action ofbreathing in the chamber 6 or in the case of overpressure in the chamber6 relative to the surrounding area is directed toward the outside or ina direction facing away from the inside space of the chamber 6.

It is thus preferred that the wall section 81 can be deflected ordeviated at least partially under the action of breathing in, out,and/or through the chamber 6. The deflection or deviation is carried outpreferably by material deforming or material expansion. The latter ispreferably carried out elastically or reversibly, so that an indicationof respiratory activity can be implemented in multiple ways. A materialdeforming or material expansion or other movement or deviation of thewall section 81 is preferably more than 0.5 mm, in particular more than1 mm or 2 mm, in the illustrated embodiment more than 3 mm, and/or lessthan 20 mm, preferably less than 15 mm, and in particular less than 10mm. Such a material deforming or material expansion or other deviationis optically readily detectable. Too large material expansion can,however, result in the formation of volume differences of the chamber 6or in an influencing of the flow characteristic of the chamber 6 bychanging the flow wall. Disruptions of the flow path can result in anincreased deposition of aerosol components on the chamber wall 82, i.e.,in a loss of active ingredient.

The wall section 81 can have multiple stable states. In particular, thewall section 81 can occupy (only) two stable states, in which the wallsection 81 is curved in each case. For example, the wall section 81 canhave a material excess increasing inward or a curved basic shape. If theshape of the wall section 81 is compensated for by exerting a force, forexample by a pressure differential, the wall section 81 turns into areverse shape. Such an unstable or changing behavior offers theadvantage that a strong movement of the change can readily be detectedby eye over a comparatively short time. As an alternative or inaddition, an acoustic signal or the like can also be generated by achange in the shape direction. As an alternative or in addition, therespiratory sensor 80 can thus acoustically signal respiration.

The wall section 81 is thus preferably designed to turn or to changefrom a concave to a convex shape or vice versa, preferably under theaction of breathing in, out, or through the chamber 6 or by the pressuredifferential that acts on the wall section 81. The inhaler 1 ispreferably designed so that in the case of an intake process in thechamber 6 relative to the surrounding area, an underpressure results,which is considerably greater than 0.2 hPa, preferably greater than 0.5hPa, and in particular greater than 1 or 2 hPa. As an alternative or inaddition, it is provided that the underpressure is considerably lessthan 10 hPa, preferably less than 5 hPa, and in particular less than 4or 3 hPa. A pressure differential of more than 0.2 or 0.5 hPa isadvantageous in order to make possible a sufficient deviation, deformingor movement of the wall section 81. In the case of an underpressure ofmore than 1 or 2 hPa, an indication of the respiratory activity isespecially easy by a comparatively large deforming of the wall section81. An underpressure of less than 10, 6 or 5 hPa is preferred since theunderpressure accompanies a corresponding intake resistance for thepatient or other user of the inhaler 1—a correspondingly lowerunderpressure than an effective and complete inhalation thus supports.An underpressure of less than 4 or 3 hPa is especially preferred. Thewall section 81 is preferably designed to indicate the respiratoryactivity in the case of the described pressure differentials inparticular via a shape. The shape or maximum deviation of the wallsection 81 can lie in a range of between 0.5 mm and 20 mm in the case ofthe described pressure differentials.

The pressure differentials in an expiratory process can deviate fromthose under the action of breathing out or through the chamber 6. Theinhaler 1 preferably has the inhalation valve 66, which automaticallycloses under the action of breathing in the chamber 6. The dispensingdevice 7 is preferably designed for use in a bodily orifice, inparticular in a nose hole or nostril 9. Therefore, an expiratory processcan be carried out by an alternative bodily orifice, such as anothernose hole or the like. In the chamber 6, an overpressure or dynamicpressure results in such a case in an expiratory process in the chamber6. The pressure differential adjoining the wall section 81 due to thedynamic pressure in the chamber 6 can be less than 50 hPa, preferablyless than 40 or 30 hPa, and in particular between 5 and 15 hPa, relativeto the surrounding area of the chamber 6. Therefore, it is preferredthat the wall section 81 be designed to make possible a shape outward inthe case of corresponding pressure differentials, which allow anon-destructive indication of a respiratory activity, in particularbetween 0.5 mm and 20 mm.

In one example, the wall section 81 can be designed so that under theaction of breathing in the chamber 6, a noticeable shape of, forexample, 1 to 5 mm results; the shape in an opposite direction duringthe intake process, i.e., under the action of breathing out or throughthe chamber 6, however, precipitates comparatively little and lies, forexample, between 0 mm and 1 mm. As a result, however, even with such aconfiguration, the respiratory activity can be indicated, since at leastthe presence or absence of a deforming or movement can be detected.Thus, it may be enough that a movement and/or deforming can be detectedby eye only in the case of an expiratory process, and a beginning intakeprocess is indicated in that a deforming or movement of the wall section81 is inferred.

In a method for administering a medication, in particular the aerosol 3from the pharmaceutical agent preparation 4, the inhaler 1 is providedwith the respiration indicator 80, whereby the inhaler 1 has the chamberwall 82 that forms the chamber 6 and a dispensing device 7, whereby thedispensing device 7 for fluidic connection of the chamber 6 to thebodily orifice is introduced or inserted into the bodily orifice, or isapplied on the bodily orifice. Then, a patient can breathe throughand/or in the inhaler 1. The respiration indicator 80, which has thewall section 81 of the chamber wall 82 or is formed in this way, isobserved, and, depending on the deforming and/or movement of the wallsection 81, the dispensing of medication, in particular the forming ofaerosol, is triggered. It is a goal to start the forming of aerosol atthe beginning of an intake process so that the aerosol 3 can be inhaledas quickly and completely as possible. For example, it is observed thatthe wall section 81 has a shape or peak that faces away from the insidespace of the chamber 6, and a forming of aerosol is triggered as soon asthis shape decreases or as soon as this shape disappears or changes. Inthis way, the forming of aerosol can be synchronized in an advantageousway with the intake process.

The pressure differential between the inside and outside of the chamber6 can be determined decisively by cross-sections or fluidic propertiesof the inhalation valve 66 or the intake opening 85 of the chamber 6. Asa whole, the inhaler 1 or the intake opening 85 of the chamber 6 isdesigned to exhibit flow resistance, by which under the action ofbreathing in, out, or through the chamber 6, an underpressure and/oroverpressure can be generated in the chamber 6 relative to thesurrounding area, by which the wall section 81 can be deformed and/ormoved.

The ability to detect deforming or movement of the wall section 81 issupported by the respiration indicator 80 having an indicator means 84.The indicator means 84 can be designed to react with the deforming ormovement of the wall section 81, in particular by a change in the coloror color intensity, a change in the reflection or transmissionproperties relative to visible light, by (enhanced) movement, and/oracoustically. For example, a hologram can be applied to the wall section81 that produces color and reflection changes even in the case of verysmall positional changes of areas of the wall section 81, which changescan be clearly detectable by eye even if the movement or deforming wasdifficult to detect as such with the naked eye. As an alternative, a pinor arm can be provided in the area of the wall section 81, and said pinor arm converts the deforming or movement of the wall section 81 into amore significant movement.

The wall section 81 can be inserted or is insertable, preferably byfriction, into the chamber wall 82. Also, the wall section 81 can beconnected snugly, in particular in an airtight or pressure-sealed way,with the chamber wall 82 and sprayed, bonded, welded or clamped on thechamber wall 82. As an alternative, the wall section 81 can also beformed by the chamber wall 82. A snug fastening of the wall section 81to the chamber wall 82 has the advantage that the respiration indicator80 according to the invention draws no secondary air, which would bedisadvantageous for the transport of aerosol and furthermore could leadto active ingredient losses via eddying of the aerosol 3 guided into thechamber 6.

The respiration indicator 80, in particular the wall section 81, ispreferably arranged outside of the flow, thus the air stream ispreferably not impeded by the chamber 6 or the releasing of aerosol. Theinhaler is preferably closed or designed to be airtight between theintake opening 85 of the chamber 6 and an outlet 10 of the dispensingdevice 7.

The wall section 81 and the chamber wall 82 can have different materialsand/or material thicknesses. In this case, it is preferred that thematerial of the wall section 81 be more flexible, slightly moreexpandable, and/or thinner than the material of the chamber wall 82.This makes possible a movement or deforming of the wall section 81 bywhich respiratory activity can be indicated.

The wall section 81 can have a connecting means for fastening in athrough passage 88 of the chamber wall 82. The wall section 81 can thusbe inserted or is insertable into a through passage 88 of the chamberwall 82. Preferably, the wall section 81 has a frame 86, which can limitthe wall section 81 and can have a contour that corresponds to a an endof the through passage 88 of the chamber wall 82.

The frame 86 or another connecting means is preferably designed forairtight and/or pressure-sealed connection of the wall section 81 withthe chamber wall 82. As shown, e.g., in FIGS. 11-13, the connectingmeans can include an edge with a U-shaped cross section that is designedfor encompass/receive the edge of the through passage in the chamberwall 82. As an alternative or in addition, the frame 86 can be bondedwith the chamber wall 82.

The respiration indicator 80 is preferably arranged above or facing theuser in a position of use of the inhaler 1. The inhaler 1 can beprovided in particular for use with a horse 5. In this case, it ispreferred that the dispensing device 7 be designed for use in a horse'snostril 9, whereby the position of use can relate to an inhaler 1inserted into the horse's nostril 9. The respiration indicator 80 can bearranged above and/or on the right relative to the longitudinal axis Lin the direction of flow of the inhaler 1, which can comply with thedispensing direction of the discharge nozzle 2. This enables an angle ofobservation, from which the movement of the wall section 81 isespecially easy to observe.

The wall section 81 can have a surface area that is larger than 0.5 cm²,preferably larger than 1 cm², in particular larger than 2 cm², and/orsmaller than 25 cm², preferably smaller than 20 cm², and in particularsmaller than 15 cm². In the case of a larger surface area of the wallsection 81, greater deviations at the same pressure differential can begenerated, which promotes a clearness of display of the respirationindicator 80. A very large wall section 81, however, leads to the factthat the flow geometry of the inhaler 1 can change based on the pressuredifferential between the inside space of the chamber 6 and thesurrounding area, which at least in the case of more significant changescan lead to an increased condensation of the pharmaceutical agentpreparation 4 from the aerosol 3. Furthermore, a very large wall section81 can lead to instabilities of the chamber 6. The preferred valuestherefore represent a good compromise between the advantages anddisadvantages that are connected with different surface areas of thewall section 81.

The wall section 81 can continue a jacket line or contour line of thechamber wall 82 adjoining the wall section 81 without a pressuredifferential between the inner and outer sides and/or can align with thechamber wall 82 adjoining the wall section 81. This makes possible anoutside shape of the chamber 6 that is uniform in a state of restwithout a pressure differential; this reduces susceptibility tocontamination and furthermore is also aesthetically advantageous.

The wall section 81 can have a sealing surface for attachment to aboundary of the through passage 88, whereby the sealing surface isdesigned to be attached snugly to the boundary of the through passage 88when inserting the wall section into the through passage 88.

In the case of an air-volume stream of between 300 l/h and 6,000 l/h,preferably between 600 l/h and 3,000 l/h, the inhaler 1 can be designedto generate a pressure loss or underpressure in the chamber 6 that isgreater than 0.5 hPa, preferably greater than 1 hPa, in particulargreater than 2 hPa, and/or less than 10 hPa, preferably less than 6 hPa,and in particular less than 4 hPa.

The wall section 81 can have an elastomer, latex, nitrile rubber,neoprene, polyurethane, styrene-ethylene-butadiene-styrene,styrene-butadiene rubber and/or silicone, or can be at least essentiallyformed therefrom. The wall section 81 can have a material—or be formedtherefrom—which has an elasticity module of smaller than 0.1 kN/mm2,preferably smaller than 0.05 kN/mm2, and in particular smaller than 0.02kN/mm2. In particular, the wall section 81 has a wall thickness that isless than 300 μm, preferably less than 200 μm, in particular less than150 μm, and/or greater than 10 μm, preferably greater than 20 μm, and inparticular, greater than 50 μm. In this way, a reliable display can beensured.

The wall section 81 can be designed to generate a mechanical stressincreasing disproportionately with increasing deviation or expansion. Inthis way, damage by overexpansion can be prevented.

The wall section 81 can be arranged at a distance from the outlet 10and/or the intake opening 85 of more than 3 cm, preferably more than 4cm, and/or less than 10 cm, preferably less than 8 cm. In this way, therespiration indicator 80 is also visible during use and, moreover, isarranged so that sufficient pressure differentials occur through therespiratory process.

The wall section 81 can have a main extension surface with a surfacenormal in the center relative to the main extension direction of thewall section, whereby the normal a) is crosswise, in particularperpendicular, to a main flow direction in the area of the wall section81; b) is crosswise, in particular perpendicular, to a releasingdirection of the discharge nozzle 2; and/or c) encompasses an angle in aspraying in a main flow direction in the area of the wall section 81and/or in a spraying in the releasing direction of the discharge nozzle2, of the inhaler 1 with a releasing direction in the area of the outlet10 of the adapter, which angle is more than 30°, preferably more than40°, in particular more than 45°, and/or less than 80°, preferably lessthan 70°, and in particular less than 65°. Surprisingly enough, it hasbeen shown that at such a position, visibility and function are optimal.

According to another aspect of this invention, the respiration indicator80, in particular the wall section 81, can be used for a sealing test.In this case, the inside space of the chamber 6 can be tensionedstarting from the dispensing device 7. The inhalation valve 66 can closein such a case. The overpressure that forms can, also independently of arespiratory process, be indicated by the respiration indicator 80. Inthis way, a sealing test or the like can be performed.

The sealing test can serve in particular to check for adequate sealingbetween the chamber 6 and the dispensing device 7, between the chamber 6and the housing 14, and/or between the housing 14 or the chamber 6 andthe inhalation valve 66. In this case, the inside space formed by thechamber 6 and/or the dispensing device 7 can be tensioned and closed. Anoverpressure that is generated in this way can be indicated by therespiration indicator 80. A pressure loss can be indicated in particularby the movement or deforming of the wall section 81. In this way, aleak, which leads to a pressure loss, can be indicated by therespiration indicator 80 or the wall section 81.

According to another aspect of this invention, the respiration indicator80 can be designed in a continuous display of the respiratory activityand/or pressure change between the inside space of the chamber 6 and thesurrounding area. In particular, breathing in, out, and/or through thechamber 6 leads to a continuous pressure fluctuation corresponding tothe respiratory activity. Such a continuous pressure fluctuation canadvantageously be indicated continuously by the respiration indicator 80according to the invention. In this way, it is possible to differentiatein an advantageous way between multiple sections, in addition to therespiratory direction, even within the intake and expiratory phases.This makes possible an especially exact determination of a triggeringtime. As an alternative or in addition to this, the respirationindicator 80 can be designed to indicate respiratory activityanalogously, in particular by a deviation, position and/or deformingthat is/are at least essentially continuous and/or correspond(s) to thepressure differential between the inside space and the surrounding areaof the chamber 6. However, other solutions are also possible.

The different aspects of this invention can be achieved bothindividually and combined. In particular, the tensioning mechanism 28can also be realized for triggering an MDI or independently by an SMI.Furthermore, the inhalation valve 66 can also be used for other purposesbeyond the inhalers and can be realized individually. The indicator 48according to the invention can likewise also be realized individuallyand independently for displaying already released or still availablepharmaceutical doses, preferably in combination with a triggeringmechanism. The same is true for the respiration indicator 80, which canalso be integrated in a wall of other devices. Synergistic effectsresult in particular in a combination of the tensioning mechanism 28,triggering concept and/or indicator 48 with a metering ring 50 owing tothe resource-conserving multiple use of components.

FIG. 14 shows the respiration indicator 80, according to the invention,in a variant of the manner in which the respiration indicator 80 ispreferably connected to the chamber 6 in a resting manner. In FIG. 14,the respiration indicator 80 is shown in the rest position. As the restposition, reference is preferably made to a state of the respirationindicator 80 in which the internal pressure corresponds at leastessentially to the ambient pressure of the chamber 6. In the restposition, the wall section 81 is preferably at least essentially levelor flat.

FIG. 15 shows the deviation of the wall section 81 in the case ofoverpressure in the chamber 6, breathing in the chamber 6 and/or inexpiratory position. FIG. 16 shows the deviation of the wall section 81in the case of underpressure in the chamber 6, with breathing out orthrough the chamber 6 and/or in the inhalation position.

The respiration indicator 80 is designed to signal breathing in, outand/or through the chamber 6 by display of the pressure differentialbetween the inside space and the surrounding area of the chamber 6. Inthis connection, in addition to the explanations, further reference ismade to FIGS. 11 to 13. The features and properties of the respirationindicator 80 from FIGS. 14 to 16 preferably correspond to thosepreviously explained in connection with FIGS. 11 to 13 and vice versa.In particular, the respiration indicator 80 from FIGS. 14 to 16 can alsohave an indicator means 84.

It is preferred that the chamber 6 be deformable only in the area of thewall section 81 by respiratory activity. Preferably, the chamber 6 ispredominantly or at least essentially dimensionally stable. Inparticular, the chamber wall 82 predominantly or at least essentially isstable so that a deforming of the chamber 6 or the chamber wall 82 isprevented by differential pressures between the inside space and thesurrounding area of the chamber 6, which can be realized under theaction of breathing.

The at least essentially dimensionally-stable part of the chamber 6preferably has the through passage 88. The through passage 88 ispreferably sealed airtight by the wall section 81. The wall section 81is, as already explained previously, preferably flexible in such a waythat breathing that is done in, out or through the chamber 6 or apressure differential realized in this way between the inside space ofthe chamber 6 and the surrounding area of the chamber 6 results in apreferably visible deforming of the wall section 81.

The wall section 81 or a part thereof that can be deformed byrespiratory activity preferably has a surface area that is less than20%, preferably less than 15%, in particular less than 10% of thesurface area of the chamber wall 82 and/or the surface of the chamber 6.It is preferred that the chamber 6 be more than 80%, preferably morethan 85%, and in particular more than 90% dimensionally stable. The wallsection 81 preferably comprises less than 20% or 15%, in particular lessthan 10%, of the chamber wall 82 that forms the chamber 6. In this way,it can be avoided in an advantageous manner that the flow geometry ofthe inside space of the chamber 6 is influenced under the action of therespiratory activity in, from or through the chamber 6.

It has been shown that, in the case of deformability of larger areas ofthe chamber wall 82, the flow properties of the chamber 6 depend on therespective position of the chamber wall 82. As a consequence, anincreased or non-reproducible amount of pharmaceutical agent preparation4 condenses on the chamber wall 82 and consequently is not released. Inthe case of the approach according to the invention, in which only thewall section 81 is deformable and the wall section 81 occupies only asmall portion of the entire chamber wall 82, the flow geometry of thechamber 6 is at least essentially independent of the deforming of thewall section 81. This advantageously results in low and reproducibleactive ingredient losses and consequently in an exact, reliable andreproducible metering.

In FIGS. 14 to 16, the respiration indicator 80 or the wall section 81according to the invention is held in a resting manner on the chamber 6.To this end, the chamber 6 in the illustrated embodiment has aconnecting section 87, to which the wall section 81 can be clipped orlocked. The connecting section 87 preferably surrounds the throughpassage 88, in particular continuously. In the illustrated embodiment,the connecting section 87 surrounds the through passage 88 of thechamber 6 in an annular and/or frame-like manner. The connecting section87 is preferably designed to be in the form of a flange or socket. Theconnecting section 87 is preferably molded-on or in with the chamberwall 82 or formed in one piece with the chamber wall 82. Here, inprinciple, however, other solutions are also possible, for example aconnecting section 87 that is screwed, glued or welded to the chamber 6or connected to the chamber 6 in some other way.

The connecting section 87 preferably comprises an undercut orindentation 89. The undercut or indentation 89 is preferably designed tohold the wall section 81 in a particularly positive, non-positive and/orresting manner. In the illustrated embodiment according to FIG. 14, thewall section 81 is engaged in the undercut or indentation 89. In thisway, the wall section 81 can be held on the chamber 6 and/or connectedto the chamber 6.

Alternatively or additionally, the wall section 81 is bonded, inparticular glued, welded, formed and/or molded, to the chamber 6.Preferably, the wall section 81 is bonded to the connecting section 87.The wall section can be bonded to the wall section 81 and/or the chamber6 at the connecting section 87 or the undercut or indentation 89.

Gluing the wall section 81 to the chamber 6 can provide advantagesregarding a flexible or elastic connection, which can be non-permanentor detachable. Welding the wall section 81 to the chamber 6 can provideadvantages regarding a very durable, permanent connection. Forming ormoulding the wall section on the chamber 6 can provide advantagesregarding a durable and reliable airtight connection, where providingthe undercut or indentation 89 does not need to be provided.

Particularly preferably, the wall section 81 is bonded to the chamber 6and/or to the connecting section 87 and/or to the undercut orindentation 89 in addition to a form fit of the wall section 81 with thechamber 6 and/or to the connecting section 87 and/or to the undercut orindentation 89. This enables an even more reliable and durableconnection.

Preferably, the chamber 6 and/or the connecting section 87 comprising aprojection 91. The projection 91 surrounds the through passage 88preferably on a radial outer side. In this case, the projection 91preferably forms a bead that is directed radially outward and/or thatextends preferably continuously. The projection 91 preferably forms theundercut or indentation 89. As an alternative or in addition, however,the undercut or indentation 89 can also be formed by one or more lockingcatches or in some other way. The forming of the undercut or indentation89 by the projection 91, in particular the projection 91 that runscontinuously around the through passage 88, offers the advantage,however, of a secure fixing of the wall section 81 while achieving goodsealing action simultaneously.

In the illustrated embodiment of FIG. 14 to FIG. 16, the wall section 81is clipped or locked to the connecting section 87 or positively held insome other way on the connecting section 87. A fastening section 90 ofthe wall section 81 preferably engages in the connecting section 87 orthe undercut or indentation 89. In this way, the wall section 81 can beheld in a secure and airtight manner on the chamber 6 in an advantageousway.

The connecting section 87, in particular the projection 91, ispreferably encompassed by the fastening section 90 of the wall section81. In this way, a preferred airtight clipping or locking connectionbetween the wall section 81 and the other chamber wall 82 can berealized.

The clipping or locking of the wall section 81 to the connecting section87 of the chamber 6 offers the advantage of a simple assembly andinterchangeability of the wall section 81. In particular, a defectivewall section 81 can also be interchangeable in an advantageous way bythe end-user on the spot.

The wall section 81 preferably comprises an elastic material,impermeable material or rubber-like material or is comprised thereof.Preferably, the wall section 81 in the fastening section 90 has a highermaterial strength than in an area overlapping the through passage 88. Inthis way, a more reliable holding of the wall section 81 can be ensured.

FIGS. 17 and 18 show a view of a pressure generator 20 and the actuatinglever 26 of the inhaler 1 according to another embodiment. In FIG. 19,the pressure generator 20 is shown with the pivot arm 55. FIG. 20 showsthe pivot arm 55 without the pressure generator 20. FIGS. 21 to 24 showviews of the pressure generator 20 with the actuating lever 26 indifferent positions.

Hereinafter, only essential differences and characteristics are dealtwith in comparison to the above-explained inhaler 1. Components that arenot depicted or not depicted in detail are preferably realized asexplained above. This also applies for the indicator 48, which is notprovided in the variant according to FIGS. 17 to 24, but can be realizedas described above. In a corresponding way, a combination with one ormore of the various above-described aspects and features is possible andadvantageous.

The inhaler 1, according to the invention, is preferably designed to beoperable with only one hand. This has the advantage that the second handof an operator is available for other activities, in particular holdinga horse 5.

An aspect of this invention that can also be achieved independentlyrelates to an inhaler 1, preferably for insertion into a nostril 9, inparticular a nostril of a horse 5, with a pressure generator 20 that canbe driven by a tensioning device 21 for discharging a pharmaceuticalagent preparation 4, whereby the tensioning device 21 can be tensionedby movement of a tensioning part, in particular the actuating lever 26,from a first position of the tensioning part into a second position ofthe tensioning part, whereby the inhaler 1 is designed to block thedischarge of the pharmaceutical agent preparation 4 and to produce thedischarge of the pharmaceutical agent preparation 4 after movement ofthe tensioning part from the second position back into the firstposition by a repeated movement of the tensioning part from the firstposition in the direction of the second position.

The above-mentioned aspect relates to the use of the tensioning part,which is also used for tensioning the tensioning device 21, fortriggering. It surprisingly has been shown, that the use of the samepart for tensioning and triggering enables a very sturdy andresource-preserving design. In particular, no knobs that are small andthus difficult to operate under adverse conditions or sensitive parts orthe like are necessary.

The tensioning part preferably is configured such that a force F isintroducible into the tensioning part. In particular, the tensioningpart has a grip portion, a handle or part for manual operating thetensioning part. The tensioning part preferably is adapted to forward orintroduce the force F acting on the tensioning part for tensioning thetensioning device 21.

Alternatively or additionally, the tensioning part can be adapted toprepare or enable discharging the pharmaceutical agent preparation 4.Alternatively or additionally, the tensioning part can be adapted toprepare the inhalator 1 or the pressure generator 20 and/or the pumpdevice 24 for discharging the pharmaceutical agent preparation 4.

The tensioning part preferably is movable, relocatable and/or slidable,preferably repeatedly. The tensioning part preferably is movable,relocatable and/or slidable, whereby the tensioning device 21 istensioned and/or the inhaler 1, the pressure generator 20, the pumpdevice 24 and/or discharge of pharmaceutical agent preparation 4 istriggered and/or driven.

The tensioning part is especially preferably realized by the actuatinglever 26, since the latter enables both the above-explained advantagesrelative to the tensioning process as well as a precise control of thetriggering even under rough environmental conditions. As an alternativeor in addition, the tensioning part can also be realized as a knob,switch, rocker or as some other movable part.

The tensioning part, in particular the actuating lever 26, is preferablypre-tensioned in the first position, in particular the rest position,also called the resting position. In the illustrated embodiment, thereset element 47 brings about the reset into the first position and/orthe pre-tensioning into the first position. The reset element 47 is aspring, in particular a compression spring and/or a spiral spring in theillustrated embodiment of FIGS. 17 to 24.

In the embodiment of FIGS. 17 to 23, the triggering device 27 preferablycomprises the tensioning part. It is preferred that the triggeringdevice 27 be designed to enable a triggering process only in the case ofa tensioned tensioning device 21. When the tensioning device 21 isuntensioned or only pre-tensioned, the triggering device 27 preferablyprevents a triggering. The triggering device 27 is thus preferablydesigned to enable or to prevent the triggering as a function of atensioning state or a preparation or suitability for triggering and/orfor discharging the pharmaceutical agent preparation 4.

The triggering is preferably prevented when and/or as long as thetensioning device 21 has not yet reached a preset tensioning state orthe inhaler 1 is not ready or prepared in some other way for dischargingthe pharmaceutical agent preparation 4. In particular, the triggering isprevented when and/or as long as the tensioning device 21, the pressuregenerator 20, the pump element 24 and/or the holder 25 is/are not yetblocked or is/are secured against triggering.

The triggering by means of the tensioning part is preferably enabledwhen the tensioning of the tensioning device 21 reaches a presettensioning, the inhaler 1 is prepared for administering thepharmaceutical agent preparation 4, and/or when a blocking of thepressure generator 20, in particular the pump device 24 or the holder25, is carried out.

The triggering of the pump process, the pressure generation and/or thedischarge of the pharmaceutical agent preparation 4 is preferablycarried out after the tensioning process is concluded. Preferably, thetriggering is carried out only after tensioning the tensioning device 21by moving the tensioning part from the first position, in particular arest position, in an actuating direction and after the tensioning partreturns opposite the actuating direction into the first position withrepeated movement in the actuating direction.

It is preferably provided that the triggering by movement of thetensioning part, in particular from the first position, is carried outup to a trigger point.

The distance over which the tensioning part can be moved up to thetrigger point is preferably smaller than the distance that thetensioning part must be moved in the actuating direction in order totension the tensioning device 21 completely and/or to block the pressuregenerator 20, the pump device 24 and/or the holder 25. The distance upto the trigger point, at which the tensioning part induces thetriggering, is preferably less than 50%, preferably less than 40% or30%, in particular less than 20%, or 15% of the distance of thetensioning device up to a point at which the tensioning device 21 iscompletely tensioned. In this way, a quick triggering can be ensured,since triggering does not require switching hands or any major movement.

Hereinafter, the aspect of the triggering based on FIGS. 21 to 24 isexplained in more detail, in which different movement states of thetriggering device 27 are depicted. Furthermore, the invention ishereinafter explained in more detail with the tensioning lever 26 as atensioning part. The basic idea can, however, be transferred to othertensioning part.

In particular, as already explained above in connection with FIGS. 6 and7, the pivot arm 55 blocks the pressure generator 20, in particular thepump device 24 and/or the holder 25, preferably in a positive manner andpreferably when the tensioning process of the tensioning device 21 isconcluded. To this end, the pump device 24 or the holder 25 is movedaxially, preferably first against a force realized by the tensioningdevice 21, until the pivot arm 55 reaches the positive device 57, inparticular an edge or a projection of the pump device 24 or the holder25. In this way, the tensioning device 21 is tensioned. The energystored in the tensioning device 21 can drive the pressure generator 20,preferably a mechanical pump mechanism for discharging thepharmaceutical agent preparation 4.

The pivot arm 55 is preferably clamped or pre-tensioned against the pumpdevice 24 or the holder 25. As can be seen from FIGS. 17 and 18, thepivot arm 55 can be pre-tensioned with a pre-tensioning device 93, inparticular a (tension) spring, against the pump device 24 and/or theholder 25, cf. also FIG. 19.

As soon as the pivot arm 55 reaches the positive device 57, the pumpdevice 24 or the holder 25 by the tensioning process, the pivot arm 55preferably automatically forms a positive fit with the positive device57. Preferably, the forming of the positive fit is carried out by thepre-tensioning or clamping of the pivot arm 55. In this way or inanother way, the pivot arm 55 is flush with the positive device 57 orthe edge of the pump device 24 and/or the holder 25. In this way, anaxial movement brought about by the tensioning device 21 or pumpmovement of the pump device 24 or holder 25 is blocked. As analternative or in addition, however, it can also be provided that thepivot arm 55 engages in a recess or some other positive device 57 insuch a way that the discharge of the pharmaceutical agent preparation 4is blocked. In principle, other forms of blocking the pressure generator20 at the end of the tensioning process are also possible, for exampleby a lock and/or frictional connection.

A position of the pivot arm 55, in which an axial movement brought aboutby the tensioning device 21 or pump movement of the pump device 24 orholder 25 is blocked, is also referred to hereinafter as a blockingposition. A position of the pivot arm 55, in which the axial movementbrought about by the tensioning device 21 or pump movement of the pumpdevice 24 or of the holder 25 is released, is referred to hereinafter asa release position. It is thus preferred that the pivot arm 55 is movedinto the blocking position at the end of the tensioning process and intothe release position for triggering the administration of thepharmaceutical agent liquid 4. The release position is preferably astarting position from which the pivot arm 55 is moved into the blockingposition after an initial or repeated tensioning process.

A movement of the pivot arm 55 back into the release position releasesthe drive of the pump device 24 or the holder 25 by the tensioningdevice 21. Subsequently, the pressure generator 20 can be driven bymeans of the tensioning device 21. As soon as the pivot arm 55 releasesthe drive of the pump device 24 of the holder 25 by the tensioningdevice 21, the tensioning device 21 shifts the pump device 24 or theholder 25 axially, preferably exclusively by spring force or clampingforce.

The pivot arm 55 is preferably held on a shaft 92 and/or mounted topivot (cf. FIGS. 19 and 20). The shaft 92 is depicted only in sectionsin FIG. 20 and preferably in a stationary manner, in particularconnected to the housing 14, the housing section 42, or a receptacle forthe pressure generator 20, molded thereon or formed in one piece.

The pivot arm 55 is preferably mounted to pivot on the shaft 92. As analternative or in addition, the pivot arm 55 can be designed to embody alinear movement. In particular, the pivot arm 55 can also be movable bya (partial) linear movement or shifting in the blocking position and/orin the release position. The pivot arm 55 is preferably designed toblock a pressure generation with the pressure generator 20, inparticular an axial movement of the pump device 24 or the holder 25,preferably as already explained above.

In the embodiment according to FIGS. 17 to 24, the movement of the pivotarm 55 is carried out in the release position; the release and/or thetriggering of the discharge of the pharmaceutical agent preparation 4is/are preferably carried out by the actuating lever 26.

In this connection, FIG. 21 shows the actuating lever 26 in the restposition, whereby the tensioning device 21 is untensioned or onlypre-tensioned. In this starting state, the actuating lever 26 preferablyprojects from the housing 14 and/or forms a maximum pivoting angle αwith the longitudinal axis L. To tensioning the tensioning device 21,the actuating lever 26 is moved in the direction of the housing 14and/or moved in such a way that the pivoting angle α is reduced. In thisway, the tensioning device 21 is tensioned, in particular as previouslydescribed in connection with FIGS. 4 and 5.

Preferably, a triggering mechanism 27 is provided, which has atriggering element 94. The triggering element 94 is preferably coupledto the actuating lever 26, in particular hinged on the actuating lever26. The triggering element 94 is preferably a push rod.

The triggering element 94 preferably has an activating section 95 formoving the pivot arm 55 from the blocking position into the releaseposition. In FIG. 21, the activating section 95 is located at a distancefrom a preferably wedge-like shifting area 96 of the pivot arm 55.Preferably, the triggering element 94 is guided in such a way that theactivating section 95 does not move the pivot arm 55 during thetensioning process. As an alternative or in addition, the triggeringelement 94 is guided in such a way that the activating section 95 doesnot move the shifting area 96 or slides on the latter. In particular, atleast one guide means 97 is provided, on which the triggering element 94is guided in such a way that the activating section 95 runs past thepivot arm 55 or the shifting area 96. In this way, the pivot arm 55 canform the triggering blocker 46 with the triggering element 94. In theillustrated embodiment, the guide means 97 are formed by stationaryelements, in particular pins. In FIGS. 17 to 24, the guide means 97 areshown only in sections for reasons of clarity.

FIG. 22 shows the end of the tensioning process. Preferably, at the endof the tensioning process, pivoting angle β, which encompasses theactuating lever 26 with the longitudinal axis L, is minimal. At the endof the tensioning process, the pivot arm 55 furthermore forms thepositive fit with the positive device 57, which can be seen in FIG. 22in such a way that the shifting area 96 and/or the pivot arm 55 isshifted in the direction of a center axis of the pump device 24 or theholder 25.

In FIG. 23, after the tensioning process is concluded, the actuatinglever 26 is moved back into the position in which the actuating lever 26preferably projects from the housing 14 and/or encompasses a maximumpivoting angle β with the longitudinal axis L. The pivot arm 55 islocated in the blocking position, and the tensioning device 21 istensioned. In the blocking position, the shifting area 96 is preferablybrought toward the activating section 95, in particular in comparison toits position in the release position.

In FIG. 24, the pivot arm 55 has been shifted from the blocking positionby the movement of the actuating lever 26 after the conclusion of thetensioning process from its blocking position in the direction of therelease position. In this way, the drive of the pressure generator 20 istriggered with the tensioning device 21 and/or the administration of thepharmaceutical agent preparation 4.

It is preferred that when the pump device 24 begins to move, the pivotarm 55 is held in its release position. In the illustrated embodiment,the pump device 24 that slides along on the pivot arm 55 blocks themovement of the pivot arm 55 back into the blocking position. Here,however, other solutions are also possible.

Preferably, the triggering element 94 is guided in such a way that afterthe pivot arm 55 is moved into its release position, the activatingsection 95 is shifted relative to the shifting area 96 in such a waythat the pivot arm 55 is prevented from moving beyond the releaseposition. In particular, the triggering device 27 is designed in such away that after reaching the release position of the pivot arm 55, theactivating section 95 slides past the pivot arm 55 as the actuatinglever 26 continues to move in the direction of the second position or inthe triggering direction. In this way, in an advantageous manner, a hightriggering sensitivity with simultaneous sturdy design is made possible,since damage of the pivot arm 55 is prevented.

Hereinafter, additional aspects and preferred configurations relating tothe tensioning mechanism 28 are explained.

According to another aspect of this invention, the inhaler 1 comprisesat least two levers 30, 35 designed for force multiplication.

Preferably, the inhaler 1 comprises a one-sided lever 35, which isdesigned for gear reduction and/or force multiplication and/or drivesthe elbow lever 30.

The lever gear 29 and/or the actuating lever 26 and/or the elbow lever30 is/are preferably designed for force multiplication.

The lever gear 29 and/or the actuating lever 26 preferably increase(s) aforce F that acts on the actuating section 40.

The lever gear 29 and/or the actuating lever 26 are preferably designedin such a way that a force F that acts on the actuating section 40 hasan increased effect on the tensioning device 21 via the lever gear 29and/or via the actuating lever 26.

The one-sided lever 35 preferably comprises a shorter lever arm 36, inparticular as a load arm, and a longer lever arm 37, in particular as aforce arm, preferably whereby the shorter lever arm 36 corresponds atleast essentially to a lever arm 32 of the elbow lever 30.

The lever gear 29 is preferably designed in such a way that with auniform force F that acts on the actuating section 40 with increasingdeviation of the actuating lever 26 in the actuating direction, theforce that acts on the tensioning device 21 increases. As an alternativeor in addition, the lever gear 29 is designed to tensioning thetensioning device 21, preferably accomplished by a spring, in particulara compression spring, as the deviation of the actuating lever 26increases in the actuating direction, whereby as the tensioning of thetensioning device 21 increases, the force that is to be exerted on theactuating section 40 of the actuating lever 26 or that is realized bythe actuating section 40 of the actuating lever 26 decreases.

Preferably, the lever gear 29 comprises at least two levers, inparticular the elbow lever 30 and the one-sided lever 35, or it isdesigned in at least two stages. In particular, the lever gear 29 isreduced in multiple stages, or the gear reduction ratio, i.e., the ratiobetween the drawn-off or resulting and fed force, in one or more stages,in particular each stage, of the lever gear 29 is greater than or equalto 1.

The one-sided lever 35 is especially preferably designed as the firststage of the lever gear 29, and the elbow lever 30 is designed as thesecond stage of the lever gear 29. However, other design solutions arealso possible.

The one-sided lever 35 preferably produces a reduction gear or forcemultiplication of the force F that is fed by the user to the one-sidedlever 35 and that acts on the inhaler 1, whereby the gear ratio of theone-sided lever 35 has in particular a constant value of greater than orequal to 1. Consequently, the force F′ that is drawn off or that iscaused by the one-sided lever 35 is preferably greater than or equal tothe supplied force F.

The elbow lever 30 of a gear reduction or force multiplicationespecially preferably produces the force F′ resulting because of theone-sided lever 35 or fed to the elbow lever 30. The gear ratio of theelbow lever 30 preferably increases with increasing actuation of theinhaler 1 or the actuating lever 26 and/or is greater with increasingtensioning of the tensioning mechanism 28 or the force multiplication.The gear ratio of the elbow lever 20 preferably is always greater thanone. Preferably, the gear ratio increases with movement of the actuatinglever 26 in the actuating direction.

The elbow lever 30 is preferably hinged on one end on the housing 14.The elbow lever 30 is preferably designed to introduce force on an endhinged on the housing via a hinge in the receptacle 45 and/or the pumpdevice 24. The elbow lever 30 preferably produces a force component inthe longitudinal direction L. The elbow lever 30 preferably directlyproduces a tensioning of the tensioning device 21. Preferably, the elbowlever 30, in particular directly, acts on the receptacle 45 connected ina rigid manner to the tensioning device 21.

The force F′ resulting because of the one-sided lever 35 or theactuating lever 26 or acting on the additional tensioning mechanism 28,in particular the elbow lever 30, preferably corresponds to the force Fon the actuating section 40 multiplied by the factor of the gear ratioof the one-sided lever 35.

The force F″ that results because of the elbow lever 30 or that acts onthe tensioning device 21 preferably corresponds to the force F′ thatacts on the elbow lever 30, multiplied by the factor of the gear ratioof the elbow lever 30, preferably whereby the force F′ corresponds tothe force F multiplied by the factor of the gear ratio of the one-sidedlever 35.

According to one aspect of this invention, the length of the one-sidedlever 35, the lever arm 36, the lever arm 37 and/or the actuating lever26 is variable, in particular adjustable. The longer lever arm 37 and/orthe actuating lever 26 can preferably be folded out for furtherextension and/or via a hinge or like a telescope or can be extended insome other way.

Preferably, the actuating section 40 of the actuating lever 26 has asurface structuring for protection against sliding and/or an adhesive orrough surface. In particular, the actuating section 40 is provided withan elastic or flexible and/or rubber-like layer.

The tensioning mechanism 28 is preferably designed to tension thetensioning device 21 in the case of a movement of the actuating lever 26from the rest position into the tensioned position.

The terms rest position and resting position and first position arepreferably synonymous or interchangeable. Preferably, the termstensioned position, pressure position, and second position aresynonymous to one another or interchangeable. The rest position, restingposition, first position and/or tensioned position, pressure position,and/or second position are preferably end positions.

In the case of a movement of the actuating lever 26 from the tensionedposition back into the rest position, the tensioning device 21preferably remains tensioned. By relaxing the tensioning device 21,preferably the pressure generator 20 is driven and/or the pharmaceuticalagent preparation 4 is pumped and/or discharged. This is preferablycarried out by a triggering and/or independently of the tensioningprocess.

Preferably, the actuating lever 26 can be swiveled between the pressureposition/tensioned position/first position and the resting position/restposition/second position. However, other design solutions are alsopossible, in particular in which the actuating lever 26 can be moved insome other way relative to the housing 14. In particular, designsolutions are possible in which the actuating lever 26 can be moved,preferably shifted and/or pressed, by means of a guide, in particular alinear guide, relative to the housing 14 between the pressureposition/tensioned position/first position and the resting position/restposition/second position.

The lever gear 29, in particular the actuating lever 26, can preferablybe locked, clamped or engaged in the tensioned position and/or in theresting position, for example for transport and/or in order to preventan inadvertent actuation of the actuating lever 26. The one-sided lever35 and/or its longer lever arm 37 is/are preferably formed between thepivot point 41 of the actuating lever 25 and the actuating section 40.The short lever arm 36 is preferably shorter than the long lever arm 37.Preferably, the long lever arm is more than twice as long as the shortlever arm 36.

In a preferred embodiment, the pivot point 41 of the actuating lever 26rests at least essentially on or in the vicinity of the longitudinalaxis L of the inhaler 1. In particular, the pivot point 41 is less than3 cm, preferably less than 2 cm, and in particular less than 1 cm fromthe longitudinal axis L and/or less than the length of the first leverarm 32 and/or the second lever arm 33 from the longitudinal axis L. Inthis way, the force F″ of the lever gear 29 that in particular acts onthe pump device 24 acts at least essentially on the longitudinal axis L.In this way, in an advantageous manner, a good transmission of force tothe pump device 24 and/or the tensioning device 21 can be achieved.

Preferably, the actuating lever 26 is mounted on two pivot points 41, inparticular in the manner of a fork. In particular, the actuating lever26 at least partially encompasses the chamber 6. In this way, a morecompact inhaler 1 can be achieved. However, other design solutions arealso possible.

The housing section 42 or the stop 43 preferably bounds the pivotingangle β of the actuating lever 26. In a variant, not shown, the stop 43and/or the angle that is formed between the stop 43 and the longitudinalaxis L or maximum pivoting angle β can be adjusted. For example, thestop 43 can occupy different predefined positions in order toindividually adjust the maximum pivoting angle β for different usersand/or to vary the amount of dosage. There may be different tensionedpositions and/or positions of rest that are preferably adjustable orpresettable. It is possible that the tensioning mechanism 28, inparticular because of an altered resting position, limits a movement ofthe pump device 24 or the holder 25. As an alternative or in addition,the pivot arm 55 or another triggering blocker device can then bedesigned to block the pump device 24 and/or the holder 25 in differentpositions that correspond in particular to adjustable or presettabletensioned positions.

In an alternative embodiment, the pivot point 44 or the joint 31 ismounted to move relative to the actuating lever 26, for example by meansof a floating bearing. In particular, the pivot point 44 or the joint 31can be run in an advantageous way in a guide, in particular in a linearguide, in or on the actuating lever 26.

What is claimed is:
 1. Inhaler for insertion into a nostril of a horse, comprising: an inhaler body, a pressure generator within the inhaler body and which has a tensioning device for driving the pressure generator, and with a tensioning mechanism for tensioning the tensioning device, wherein the tensioning mechanism has a lever gear for tensioning the tensioning device, wherein the lever gear comprises an actuating lever with an actuating section located outside of the inhaler body for manual actuation of the lever gear, one end of the actuating lever being connected with the inhaler body at a pivot point, and an arm within the inhaler body at a position for acting on the tensioning device, wherein the actuating lever together with the arm form an elbow lever, the arm being hinged to the actuating lever between the pivot point and said actuating section.
 2. Inhaler according to claim 1, wherein the lever gear, has at least one lever that is configured for at least one of gear reduction and force increase.
 3. Inhaler according to claim 1, wherein the elbow lever produces a direction of movement that runs in a lengthwise direction of the inhaler.
 4. Inhaler according to claim 1, wherein said one end of the actuating lever is hinged to the inhaler body at said pivot point.
 5. Inhaler according to claim 1, wherein the actuating lever has a pressure position and a resting position between which the actuating lever is pivotable, and wherein the actuating lever is movable toward the inhaler body from the resting position into the pressure position.
 6. Inhaler according to claim 1, wherein the actuating lever is configured to increase a force that acts on an actuating section of the actuating lever such that the increased force tensions the tensioning device.
 7. Inhaler according to claim 1, wherein the lever gear is configured such that, with a force acting on the actuating section, and with increasing movement of the actuating lever in an actuating direction of the actuating lever, an increasing force results that acts on the tensioning device.
 8. Inhaler according to claim 1, wherein at least one of the lever gear and the actuating lever is configured in such a way that a force that acts on the actuating section results in an increased force on the tensioning device due to said at least one of the lever gear and the actuating lever.
 9. Inhaler according to claim 1, wherein the pressure generator is configured to at least one of pressurize and spray a pharmaceutical agent preparation by energy stored in the tensioning device.
 10. Inhaler according to claim 1, wherein the pressure generator has a pump device, which is axially movable by the lever gear by which the tensioning device can be tensioned and which is configured to convey a pharmaceutical agent preparation out of a discharge nozzle in the case of a movement of the pump device caused by the tensioning device.
 11. Inhaler according to claim 10, wherein the pump device has a receptacle or a stop for the arm, wherein the tensioning mechanism is configured so that the arm acts on the pump device in a tensioning movement of the lever gear, so that a force can be introduced into the tensioning device.
 12. Inhaler according claim 1, wherein the inhaler has a triggering device, wherein, when tensioning of the tensioning device is concluded, the tensioning device is securable against movement.
 13. Inhaler according to claim 5, wherein the tensioning mechanism has a reset element which is configured to tension or move the actuating lever back into the rest position.
 14. Inhaler for insertion into a nostril of a horse, comprising: a pressure generator having a tensioning device for driving the pressure generator, wherein the tensioning device is tensionable by moving a tensioning part from a first resting position of the tensioning part into a second pressurizing position of the tensioning part without producing a discharge from the inhaler, and wherein the inhaler is configured to release the tension device when tensioned, trigger the pressure generator and to discharge a pharmaceutical agent preparation by moving the tensioning part from the second position into the first position, and then moving the tensioning part from the first position toward the second position again.
 15. Inhaler according to claim 14, wherein the inhaler has a triggering device which is configured to enable or to prevent the releasing or triggering of the tensioning device depending on a tensioning state of the tensioning device.
 16. Inhaler according to claim 14, wherein the releasing or the triggering is prevented as long as the tensioning device is not in a preset tensioning state that is ready for discharging the pharmaceutical agent preparation.
 17. Inhaler according to claim 16, wherein the releasing or the triggering by means of the tensioning part is enabled when the tensioning of the tensioning device reaches said preset tensioning state.
 18. Inhaler according to claim 14, wherein the tensioning part is moveable from the first position via a triggering point into the second position, and wherein the triggering is carried out when reaching the triggering point with the tensioning part, and wherein a distance between the first position of the tensioning part and the triggering point is less than 50% of a distance of the tensioning part between the first position and the second position.
 19. Method for triggering a nebulizer or an inhaler that has a pressure generator with a tensioning device, wherein the tensioning device is configured for driving the pressure generator, wherein the method comprises the steps of: tensioning the tensioning device by moving a tensioning part from a first position into a second position without triggering dispensing from the nebulizer or inhaler, moving the tensioning part back into the first position again, and afterwards moving the tensioning part again from the first position in the direction of the second position, whereby dispensing from the nebulizer or inhaler is triggered.
 20. Method according to claim 19, wherein the triggering effects at least one of administration of a pharmaceutical agent preparation; driving a pressure generator of the inhaler; pressure generation with the pressure generator; discharging pharmaceutical agent preparation; and generating aerosol with the inhaler.
 21. Inhaler according to claim 1, wherein at least one of the lever gear and the actuating lever is configured in such a way that a force that acts on an actuating section results in an increased force on the tensioning device due to said elbow lever.
 22. Inhaler according to claim 14, wherein the releasing or the triggering is prevented as long as the tensioning device is as long as the inhaler is ready for discharging the pharmaceutical agent preparation.
 23. Inhaler according to claim 14, wherein the inhaler is configured to block at least one of the pressure generator, the tension device when tensioned, and discharge of a pharmaceutical agent preparation in the inhaler. 